Low level light therapy for enhancement of neurologic function of a patient affected by Parkinson's disease

CLAIM OF PRIORITY

This application also claims the benefit of U.S. Provisional Application No. 60/840,370, filed Aug. 24, 2006, which is incorporated in its entirety by reference herein.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present application relates to systems and methods for enhancing neurologic function such as may be desired in individuals having a loss of such function, including motor function and cognitive function, including that resulting from Parkinson's disease.

2. Description of the Related Art

Parkinson's disease is a chronic, progressive neurodegenerative disease or movement disorder that affects up to one million people in the United States. Parkinson's disease affects neurologic function by degrading motor skills of the subject and by causing dementia. The pathology of Parkinson's disease includes reduced formation and action of dopamine, which is produced in the dopaminergic neurons of the brain. Previous research of the causes and possible treatments of Parkinson's disease have been directed towards efforts to compensate for the reduced formation and action of dopamine caused by the disease.

Dementia (e.g., as resulting from Parkinson's disease) is a collection of symptoms but it is not itself a disease. It is characterized as the loss of cognitive function having a severity so as to interfere with a person's daily activities. Cognitive function includes activities such as knowing, thinking, learning, memory, perception, and judging. Symptoms of dementia can also include changes in personality, mood, and behavior of the subject. Although, in some cases, dementia can be cured by curing the underlying disease (e.g. infection, nutritional deficiency, tumor), in most cases dementia is considered incurable.

High energy laser radiation is now well accepted as a surgical tool for cutting, cauterizing, and ablating biological tissue. High energy lasers are now routinely used for vaporizing superficial skin lesions and, to make deep cuts. For a laser to be suitable for use as a surgical laser, it must provide laser energy at a power sufficient to heart tissue to temperatures over 50° C. Power outputs for surgical lasers vary from 1-5 W for vaporizing superficial tissue, to about 100 W for deep cutting.

In contrast, low level laser therapy involves therapeutic administration of laser energy to a patient at vastly lower power outputs than those used in high energy laser applications, resulting in desirable biostimulatory effects while leaving tissue undamaged. For example, in rat models of myocardial infarction and ischemia-reperfusion injury, low energy laser irradiation reduces infarct size and left ventricular dilation, and enhances angiogenesis in the myocardium. (Yaakobi et al., <i>J. Appl. Physiol. </i>90, 2411-19 (2001)). Low level laser therapy has been described for treating pain, including headache and muscle pain, and inflammation.

SUMMARY OF THE INVENTION

In certain embodiments, a method of treating a patient having neurologic function affected by Parkinson's disease is provided. The method comprises providing a patient having neurologic function affected by Parkinson's disease. The method further comprises delivering electromagnetic radiation noninvasively through the scalp and the skull of the patient to at least one portion of the brain of the patient. The light energy has a wavelength in the visible to near-infrared wavelength range, and the wavelength, power density, and amount of the light energy delivered to the at least one portion of the brain are sufficient to reduce the severity of symptoms of Parkinson's disease in the patient.

In certain embodiments, a method of treating or preventing Parkinson's disease is provided. The method comprises noninvasively irradiating at least a portion of a patient's brain with electromagnetic radiation transmitted through the scalp. The electromagnetic radiation has a power density between 0.01 mW/cm²and 100 mW/cm²at a depth of approximately 2 centimeters below the dura.

In certain embodiments, a method of treating a patient is provided. The method comprises delivering electromagnetic radiation noninvasively through the scalp and the skull to at least one portion of the brain of the patient. The light energy has a wavelength in the visible to near-infrared wavelength range, and the wavelength, power density, and amount of the light energy delivered to the at least one portion of the brain are sufficient to prevent, reduce the severity, or reduce the incidence of Parkinson's disease in the patient.

In certain embodiments, a method of preventing Parkinson's disease in a patient is provided. The method comprises providing a patient having a predisposition towards contracting Parkinson's disease. The method further comprises delivering electromagnetic radiation noninvasively through the scalp and the skull of the patient to at least one portion of the brain of the patient. The light energy has a wavelength in the visible to near-infrared wavelength range, and the wavelength, power density, and amount of the light energy delivered to the at least one portion of the brain are sufficient to reduce a probability of the patient contracting Parkinson's disease.

In certain embodiments, a method of treating the central nervous system of a patient is provided. The method comprises identifying a patient exhibiting symptoms of damage to the central nervous system due to Parkinson's disease. The method further comprises irradiating an in vitro culture comprising progenitor cells with electromagnetic radiation having a wavelength in the visible to near-infrared wavelength range and a power density of at least about 0.01 mW/cm². The method further comprises implanting the irradiated cells into the central nervous system of the patient.

For purposes of summarizing the present invention, certain aspects, advantages, and novel features of the present invention have been described herein above. It is to be understood, however, that not necessarily all such advantages may be achieved in accordance with any particular embodiment of the present invention. Thus, the present invention may be embodied or carried out in a manner that achieves or optimizes one advantage or group of advantages as taught herein without necessarily achieving other advantages as may be taught or suggested herein.

BRIEF DESCRIPTION OF THE DRAWINGS

<figref idrefs="DRAWINGS">FIG. 1</figref> schematically illustrates a therapy apparatus comprising a cap which fits securely over the patient's head.

<figref idrefs="DRAWINGS">FIG. 2</figref> schematically illustrates a fragmentary cross-sectional view taken along the lines <b>2</b>-<b>2</b> of <figref idrefs="DRAWINGS">FIG. 1</figref>, showing one embodiment of a portion of a therapy apparatus comprising an element and its relationship to the scalp and brain.

<figref idrefs="DRAWINGS">FIG. 3</figref> schematically illustrates an embodiment with an element comprising a container coupled to an inlet conduit and an outlet conduit for the transport of a flowing material through the element.

<figref idrefs="DRAWINGS">FIG. 4A</figref> schematically illustrates a fragmentary cross-sectional view taken along the lines <b>2</b>-<b>2</b> of <figref idrefs="DRAWINGS">FIG. 1</figref>, showing another embodiment of a portion of a therapy apparatus comprising an element with a portion contacting the scalp and a portion spaced away from the scalp.

<figref idrefs="DRAWINGS">FIG. 4B</figref> schematically illustrates a fragmentary cross-sectional view taken along the lines <b>2</b>-<b>2</b> of <figref idrefs="DRAWINGS">FIG. 1</figref>, showing an embodiment of a portion of a therapy apparatus comprising a plurality of light sources and an element with portions contacting the scalp and portions spaced away from the scalp.

<figref idrefs="DRAWINGS">FIGS. 5A and 5B</figref> schematically illustrate cross-sectional views of two embodiments of the element in accordance with <figref idrefs="DRAWINGS">FIG. 4B</figref> taken along the line <b>4</b>-<b>4</b>.

<figref idrefs="DRAWINGS">FIGS. 6A-6C</figref> schematically illustrate an embodiment in which the light sources are spaced away from the scalp.

<figref idrefs="DRAWINGS">FIGS. 7A and 7B</figref> schematically illustrate the diffusive effect on the light by the element.

<figref idrefs="DRAWINGS">FIGS. 8A and 8B</figref> schematically illustrate two light beams having different cross-sections impinging a patient's scalp and propagating through the patient's head to irradiate a portion of the patient's brain tissue.

<figref idrefs="DRAWINGS">FIG. 9A</figref> schematically illustrates a therapy apparatus comprising a cap and a light source comprising a light blanket.

<figref idrefs="DRAWINGS">FIGS. 9B and 9C</figref> schematically illustrate two embodiments of the light blanket.

<figref idrefs="DRAWINGS">FIG. 10</figref> schematically illustrates a therapy apparatus comprising a flexible strap and a housing.

<figref idrefs="DRAWINGS">FIG. 11</figref> schematically illustrates a therapy apparatus comprising a handheld probe.

<figref idrefs="DRAWINGS">FIG. 12</figref> is a block diagram of a control circuit comprising a programmable controller.

<figref idrefs="DRAWINGS">FIG. 13</figref> schematically illustrates a therapy apparatus comprising a light source and a controller.

<figref idrefs="DRAWINGS">FIG. 14</figref> schematically illustrates a light source comprising a laser diode and a galvometer with a mirror and a plurality of motors.

<figref idrefs="DRAWINGS">FIGS. 15A and 15B</figref> schematically illustrate two irradiation patterns that are spatially shifted relative to each other.

<figref idrefs="DRAWINGS">FIG. 16</figref> schematically illustrates an example therapy apparatus in accordance with embodiments described herein.

<figref idrefs="DRAWINGS">FIG. 17A</figref> is a graph of the effects of laser treatment of 7.5 mW/cm²for a treatment duration of 2 minutes on a population of rabbits having small clot embolic stroke.

<figref idrefs="DRAWINGS">FIG. 17B</figref> is a graph of the effects of laser treatment of 25 mW/cm²for a treatment duration of 10 minutes on a population of rabbits having small clot embolic stroke.

<figref idrefs="DRAWINGS">FIG. 18</figref> is a graph showing the therapeutic window for laser-induced behavioral improvements after small-clot embolic strokes in rabbits.

<figref idrefs="DRAWINGS">FIG. 19</figref> schematically illustrates an example apparatus which is wearable by a patient for treating the patient's brain.

<figref idrefs="DRAWINGS">FIG. 20</figref> schematically illustrates an example apparatus having a plurality of elements in accordance with certain embodiments described herein.

<figref idrefs="DRAWINGS">FIG. 21</figref> schematically illustrates an example element in an exploded view.

<figref idrefs="DRAWINGS">FIG. 22A</figref> schematically illustrates an example optical component with example dimensions in inches.

<figref idrefs="DRAWINGS">FIGS. 22B and 22C</figref> schematically illustrate other example optical components in accordance with certain embodiments described herein.

<figref idrefs="DRAWINGS">FIG. 23</figref> schematically illustrates an example first support ring with example dimensions in inches.

<figref idrefs="DRAWINGS">FIG. 24</figref> schematically illustrates an example second support ring with example dimensions in inches.

<figref idrefs="DRAWINGS">FIG. 25</figref> schematically illustrates an example label compatible with certain embodiments described herein.

<figref idrefs="DRAWINGS">FIGS. 26A and 26B</figref> schematically illustrate an example labeling configuration for the apparatus on the left-side and right-side of the apparatus.

<figref idrefs="DRAWINGS">FIG. 26C</figref> schematically illustrates the example labeling configuration of <figref idrefs="DRAWINGS">FIGS. 26A and 26B</figref> from above a flattened view of the apparatus.

<figref idrefs="DRAWINGS">FIGS. 27A-27E</figref> schematically illustrate various stages of structures formed during the fabrication of the apparatus of <figref idrefs="DRAWINGS">FIGS. 20-25</figref>.

<figref idrefs="DRAWINGS">FIG. 28</figref> schematically illustrates an apparatus which emits light for irradiating a patient's skin to treat portions of a patient's body underneath the patient's skin.

<figref idrefs="DRAWINGS">FIG. 29</figref> schematically illustrates an example optical conduit optically coupled to an example optical device.

<figref idrefs="DRAWINGS">FIG. 30</figref> schematically illustrates a simplified optical device compatible with certain embodiments described herein.

<figref idrefs="DRAWINGS">FIG. 31A</figref> illustrates two beam profile cross-sections of a light beam emitted from the optical device of <figref idrefs="DRAWINGS">FIG. 29</figref> with the planes of the two cross-sections of <figref idrefs="DRAWINGS">FIG. 31A</figref> generally perpendicular to one another and to the output optical element.

<figref idrefs="DRAWINGS">FIG. 31B</figref> illustrates the encircled energy of a light beam emitted from the optical device of <figref idrefs="DRAWINGS">FIG. 29</figref>.

<figref idrefs="DRAWINGS">FIG. 32A</figref> illustrates two beam profile cross-sections of a light beam emitted from the optical device of <figref idrefs="DRAWINGS">FIG. 30</figref> having a smooth gold-plated conical inner surface.

<figref idrefs="DRAWINGS">FIG. 32B</figref> illustrates the encircled energy of a light beam emitted from the optical device of <figref idrefs="DRAWINGS">FIG. 30</figref>.

<figref idrefs="DRAWINGS">FIG. 33</figref> illustrates two beam profile cross-sections of a light beam emitted from the optical device of <figref idrefs="DRAWINGS">FIG. 30</figref> having a grit sandblasted conical inner surface.

<figref idrefs="DRAWINGS">FIGS. 34A and 34B</figref> illustrate the beam divergence for the optical device of <figref idrefs="DRAWINGS">FIG. 29</figref> and of <figref idrefs="DRAWINGS">FIG. 30</figref> (with a sandblasted inner surface), respectively.

<figref idrefs="DRAWINGS">FIG. 35</figref> is a flow diagram of an example method for controllably exposing at least one predetermined area of a patient's scalp to laser light to irradiate the patient's brain.

<figref idrefs="DRAWINGS">FIG. 36</figref> is a graph which shows mediators responsible for ischemic stroke tissue damage and the time points at which they occur.

<figref idrefs="DRAWINGS">FIG. 37</figref> is a schematic diagram of the electron transport chain in mitochondria.

<figref idrefs="DRAWINGS">FIG. 38</figref> is a graph of cell proliferation and cytochrome oxidase activity percentage as functions of the wavelength of light used to stimulate mammalian cells.

<figref idrefs="DRAWINGS">FIG. 39</figref> is a graph of the transmittance of light through blood (in arbitrary units) as a function of wavelength.

<figref idrefs="DRAWINGS">FIG. 40</figref> is a graph of the absorption of light by brain tissue.

<figref idrefs="DRAWINGS">FIG. 41</figref> is a graph of the efficiency of energy delivery as a function of wavelength.

<figref idrefs="DRAWINGS">FIG. 42</figref> is a bar graph of the absorption of 808 nanometer light through various rat tissues.

<figref idrefs="DRAWINGS">FIG. 43</figref> is a graph of the power density versus the depth from the dura for an input power density of 10 mW/cm².

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Certain embodiments described herein for low level light therapy methods for enhancing neurologic function are based in part on the new and surprising discovery that power density (i.e., power per unit area) of the light energy applied to tissue appears to be a very important factor in determining the relative efficacy of low level light therapy, and particularly with respect to enhancing the function of neurons in both healthy and diseased states.

Certain embodiments described herein provide methods directed toward the enhancement of neurologic function in a subject. The methods include delivering a neurologic enhancing effective amount of a light energy having a wavelength in the visible to near-infrared wavelength range to at least one area of the brain of a subject. In certain embodiments, delivering the neurologic function enhancing effective amount of light energy includes delivering a predetermined power density of light energy through the skull to the target area of the brain and/or delivering light energy through the skull to at least one area of the brain of a subject, wherein the wavelength, power density and amount of the light energy delivered are sufficient to cause an enhancement of neurologic functioning.

Low level light therapy (“LLLT”) or phototherapy involves therapeutic administration of light energy to a patient at lower power outputs than those used for cutting, cauterizing, or ablating biological tissue, resulting in desirable biostimulatory effects while leaving tissue undamaged. In non-invasive phototherapy, it is desirable to apply an efficacious amount of light energy to the internal tissue to be treated using light sources positioned outside the body.

Laser therapy has been shown to be effective in a variety of settings, including treating lymphoedema and muscular trauma, and carpal tunnel syndrome. Recent studies have shown that laser-generated infrared radiation is able to penetrate various tissues, including the brain, and modify function. In addition, laser-generated infrared radiation can induce angiogenesis, modify growth factor (transforming growth factor-β) signaling pathways, and enhance protein synthesis.

However, absorption of the light energy by intervening tissue can limit the amount of light energy delivered to the target tissue site, while heating the intervening tissue. In addition, scattering of the light energy by intervening tissue can limit the power density or energy density delivered to the target tissue site. Brute force attempts to circumvent these effects by increasing the power and/or power density applied to the outside surface of the body can result in damage (e.g., burning) of the intervening tissue.

Non-invasive phototherapy methods are circumscribed by setting selected treatment parameters within specified limits so as to preferably avoid damaging the intervening tissue. A review of the existing scientific literature in this field would cast doubt on whether a set of undamaging, yet efficacious, parameters could be found. However, certain embodiments, as described herein, provide devices and methods which can achieve this goal.

Such embodiments may include selecting a wavelength of light at which the absorption by intervening tissue is below a damaging level. Such embodiments may also include setting the power output of the light source at very low, yet efficacious, power densities (e.g., between approximately 100 μW/cm²to approximately 10 W/cm²) at the target tissue site, and time periods of application of the light energy at a few seconds to minutes to achieve an efficacious energy density at the target tissue site being treated. Other parameters can also be varied in the use of phototherapy. These other parameters contribute to the light energy that is actually delivered to the treated tissue and may play key roles in the efficacy of phototherapy. In certain embodiments, the irradiated portion of the brain can comprise the entire brain.

In certain embodiments, a method treats a subject suffering from Parkinson's disease. The method includes delivering light energy having a wavelength in the visible to near-infrared wavelength range through the skull to at least one target area of the brain of the subject, wherein the wavelength, power density and amount of the light energy delivered are sufficient to prevent, reduce the severity, or reduce the incidence of Parkinson's disease in the subject.

In certain embodiments, the target area of the brain may be all of the brain or a specific area of the brain including, but not limited to, an area associated with a particular cognitive or motor function, an area exhibiting neurodegeneration, the cortex, and/or an area that has been affected by trauma. The subject may have a cognitive or motor impairment such as from neurodegeneration or the subject may be normal.

In certain embodiments, the predetermined power density is a power density of at least about 0.01 mW/cm². The predetermined power density in certain embodiments is typically selected from the range of about 0.01 mW/cm²to about 100 mW/cm², including from about 0.01 mW/cm²to about 15 mW/cm²and from about 2 mW/cm²to about 50 mW/cm². In certain embodiments, power densities above or below these values may be used.

In certain embodiments, the methods encompass using light energy having a wavelength of about 630 nanometers to about 904 nanometers, and in certain embodiments the light energy has a wavelength of about 780 nanometers to about 840 nanometers. The light energy is preferably from a coherent source (i.e. a laser), but light from non-coherent sources may also be used.

In certain embodiments, the methods encompass placing a light source in contact with a region of skin that is either adjacent an area of the brain in which treatment is desired, contralateral to such area, or a combination of the foregoing, and then administering the light energy, including the neurologic function enhancing effective amount of light energy, as may be measured by power density, to the target area of the brain. In delivering the light, the power density may be a predetermined power density. In certain embodiments, a surface power density of the light energy sufficient for the light energy to penetrate the skull is determined. The determination of the required surface power density, which is relatively higher than the power density to be delivered to the brain tissue being treated, takes into account factors that attenuate power density as it travels through tissue, including skin pigmentation, and location of the brain area being treated, particularly the distance of the brain area from the skin surface where the light energy is applied.

In certain embodiments, a method increases the production of adenosine triphosphate (ATP) by neurons to increase neurologic function. The method comprises irradiating neurons with light energy having a wavelength in the near infrared to visible portion of the electromagnetic spectrum for at least about 1 second, where the power density of said light energy at the neurons is at least about 0.01 mW/cm².

While certain embodiments of phototherapy are described herein in conjunction with various theories and potential action mechanisms, as they presently appear to the inventors, the scope of the claims of the present application is not to be construed to depend on the accuracy, relevance, or specifics of any of these theories or potential action mechanisms. Thus the claims of the present application are to be construed without being bound by theory or by a specific mechanism.

Element to Inhibit Temperature Increases at the Scalp

<figref idrefs="DRAWINGS">FIGS. 1 and 2</figref> schematically illustrate an embodiment of a therapy apparatus <b>10</b> for treating a patient's brain <b>20</b>. The therapy apparatus <b>10</b> comprises a light source <b>40</b> having an output emission area <b>41</b> positioned to irradiate a portion of the brain <b>20</b> with an efficacious power density and wavelength of light. The therapy apparatus <b>10</b> further comprises an element <b>50</b> interposed between the light source <b>40</b> and the patient's scalp <b>30</b>. The element <b>50</b> is adapted to inhibit temperature increases at the scalp <b>30</b> caused by the light.

As used herein, the term “element” is used in its broadest sense, including, but not limited to, as a reference to a constituent or distinct part of a composite device. In certain embodiments, the element <b>50</b> is adapted to contact at least a portion of the patient's scalp <b>30</b>, as schematically illustrated in <figref idrefs="DRAWINGS">FIGS. 1-4</figref>. In certain such embodiments, the element <b>50</b> is in thermal communication with and covers at least a portion of the scalp <b>30</b>. In other embodiments, the element <b>50</b> is spaced away from the scalp <b>30</b> and does not contact the scalp <b>30</b>.

In certain embodiments, the light passes through the element <b>50</b> prior to reaching the scalp <b>30</b> such that the element <b>50</b> is in the optical path of light propagating from the light source <b>40</b>, through the scalp <b>30</b>, through the bones, tissues, and fluids of the head (schematically illustrated in <figref idrefs="DRAWINGS">FIG. 1</figref> by the region <b>22</b>), to the brain <b>20</b>. In certain embodiments, the light passes through a transmissive medium of the element <b>50</b>, while in other embodiments, the light passes through an aperture of the element <b>50</b>. As described more fully below, the element <b>50</b> may be utilized with various embodiments of the therapy apparatus <b>10</b>.

In certain embodiments, the light source <b>40</b> is disposed on the interior surface of a cap <b>60</b> which fits securely over the patient's head. The cap <b>60</b> provides structural integrity for the therapy apparatus <b>10</b> and holds the light source <b>40</b> and element <b>50</b> in place. Example materials for the cap <b>60</b> include, but are not limited to, metal, plastic, or other materials with appropriate structural integrity. The cap <b>60</b> may include an inner lining <b>62</b> comprising a stretchable fabric or mesh material, such as Lycra or nylon. In certain embodiments, the light source <b>40</b> is adapted to be removably attached to the cap <b>60</b> in a plurality of positions so that the output emission area <b>41</b> of the light source <b>40</b> can be advantageously placed in a selected position for treatment of Parkinson's disease in any portion of the brain <b>20</b>. In other embodiments, the light source <b>40</b> can be an integral portion of the cap <b>60</b>.

The light source <b>40</b> illustrated by <figref idrefs="DRAWINGS">FIGS. 1 and 2</figref> comprises at least one power conduit <b>64</b> coupled to a power source (not shown). In some embodiments, the power conduit <b>64</b> comprises an electrical conduit which is adapted to transmit electrical signals and power to an emitter (e.g., laser diode or light-emitting diode). In certain embodiments, the power conduit <b>64</b> comprises an optical conduit (e.g., optical waveguide) which transmits optical signals and power to the output emission area <b>41</b> of the light source <b>40</b>. In certain such embodiments, the light source <b>40</b> comprises optical elements (e.g., lenses, diffusers, and/or waveguides) which transmit at least a portion of the optical power received via the optical conduit <b>64</b>. In still other embodiments, the therapy apparatus <b>10</b> contains a power source (e.g., a battery) and the power conduit <b>64</b> is substantially internal to the therapy apparatus <b>10</b>.

In certain embodiments, the patient's scalp <b>30</b> comprises hair and skin which cover the patient's skull. In other embodiments, at least a portion of the hair is removed prior to the phototherapy treatment, so that the therapy apparatus <b>10</b> substantially contacts the skin of the scalp <b>30</b>.

In certain embodiments, the element <b>50</b> is adapted to contact the patient's scalp <b>30</b>, thereby providing an interface between the therapy apparatus <b>10</b> and the patient's scalp <b>30</b>. In certain such embodiments, the element <b>50</b> is coupled to the light source <b>40</b> and in other such embodiments, the element is also adapted to conform to the scalp <b>30</b>, as schematically illustrated in <figref idrefs="DRAWINGS">FIG. 1</figref>. In this way, the element <b>50</b> positions the output emission area <b>41</b> of the light source <b>40</b> relative to the scalp <b>30</b>. In certain such embodiments, the element <b>50</b> is mechanically adjustable so as to adjust the position of the light source <b>40</b> relative to the scalp <b>30</b>. By fitting to the scalp <b>30</b> and holding the light source <b>40</b> in place, the element <b>50</b> inhibits temperature increases at the scalp <b>30</b> that would otherwise result from misplacement of the light source <b>40</b> relative to the scalp <b>30</b>. In addition, in certain embodiments, the element <b>50</b> is mechanically adjustable so as to fit the therapy apparatus <b>10</b> to the patient's scalp <b>30</b>.

In certain embodiments, the element <b>50</b> provides a reusable interface between the therapy apparatus <b>10</b> and the patient's scalp <b>30</b>. In such embodiments, the element <b>50</b> can be cleaned or sterilized between uses of the therapy apparatus, particularly between uses by different patients. In other embodiments, the element <b>50</b> provides a disposable and replaceable interface between the therapy apparatus <b>10</b> and the patient's scalp <b>30</b>. By using pre-sterilized and pre-packaged replaceable interfaces, certain embodiments can advantageously provide sterilized interfaces without undergoing cleaning or sterilization processing immediately before use.

In certain embodiments, the element <b>50</b> comprises a container (e.g., a cavity or bag) containing a material (e.g., gel or liquid). The container can be flexible and adapted to conform to the contours of the scalp <b>30</b>. Other example materials contained in the container of the element <b>50</b> include, but are not limited to, thermal exchange materials such as glycerol and water. The element <b>50</b> of certain embodiments substantially covers the entire scalp <b>30</b> of the patient, as schematically illustrated in <figref idrefs="DRAWINGS">FIG. 2</figref>. In other embodiments, the element <b>50</b> only covers a localized portion of the scalp <b>30</b> in proximity to the irradiated portion of the scalp <b>30</b>.

In certain embodiments, at least a portion of the element <b>50</b> is within an optical path of the light from the light source <b>40</b> to the scalp <b>30</b>. In such embodiments, the element <b>50</b> is substantially optically transmissive at a wavelength of the light emitted by the output emission area <b>41</b> of the light source <b>40</b> and is adapted to reduce back reflections of the light. By reducing back reflections, the element <b>50</b> increases the amount of light transmitted to the brain <b>20</b> and reduces the need to use a higher power light source <b>40</b> which may otherwise create temperature increases at the scalp <b>30</b>. In certain such embodiments, the element <b>50</b> comprises one or more optical coatings, films, layers, membranes, etc. in the optical path of the transmitted light which are adapted to reduce back reflections.

In certain such embodiments, the element <b>50</b> reduces back reflections by fitting to the scalp <b>30</b> so as to substantially reduce air gaps between the scalp <b>30</b> and the element <b>50</b> in the optical path of the light. The refractive-index mismatches between such an air gap and the element <b>50</b> and/or the scalp <b>30</b> would otherwise result in at least a portion of the light propagating from the light source <b>40</b> to the brain <b>20</b> to be reflected back towards the light source <b>40</b>.

In addition, certain embodiments of the element <b>50</b> comprise a material having, at a wavelength of light emitted by the light source <b>40</b>, a refractive index which substantially matches the refractive index of the scalp <b>30</b> (e.g., about 1.3), thereby reducing any index-mismatch-generated back reflections between the element <b>50</b> and the scalp <b>30</b>. Examples of materials with refractive indices compatible with embodiments described herein include, but are not limited to, glycerol, water, and silica gels. Example index-matching gels include, but are not limited to, those available from Nye Lubricants, Inc. of Fairhaven, Mass.

In certain embodiments, the element <b>50</b> is adapted to cool the scalp <b>30</b> by removing heat from the scalp <b>30</b> so as to inhibit temperature increases at the scalp <b>30</b>. In certain such embodiments, the element <b>50</b> comprises a reservoir (e.g., a chamber or a conduit) adapted to contain a coolant. The coolant flows through the reservoir near the scalp <b>30</b>. The scalp <b>30</b> heats the coolant, which flows away from the scalp <b>30</b>, thereby removing heat from the scalp <b>30</b> by active cooling. The coolant in certain embodiments circulates between the element <b>50</b> and a heat transfer device, such as a chiller, whereby the coolant is heated by the scalp <b>30</b> and is cooled by the heat transfer device. Example materials for the coolant include, but are not limited to, water or air.

In certain embodiments, the element <b>50</b> comprises a container <b>51</b> (e.g., a flexible bag) coupled to an inlet conduit <b>52</b> and an outlet conduit <b>53</b>, as schematically illustrated in <figref idrefs="DRAWINGS">FIG. 3</figref>. A flowing material (e.g., water, air, or glycerol) can flow into the container <b>51</b> from the inlet conduit <b>52</b>, absorb heat from the scalp <b>30</b>, and flow out of the container <b>51</b> through the outlet conduit <b>53</b>. Certain such embodiments can provide a mechanical fit of the container <b>51</b> to the scalp <b>30</b> and sufficient thermal coupling to prevent excessive heating of the scalp <b>30</b> by the light. In certain embodiments, the container <b>51</b> can be disposable and replacement containers <b>51</b> can be used for subsequent patients.

In still other embodiments, the element <b>50</b> comprises a container (e.g., a flexible bag) containing a material which does not flow out of the container but is thermally coupled to the scalp <b>30</b> so as to remove heat from the scalp <b>30</b> by passive cooling. Example materials include, but are not limited to, water, glycerol, and gel. In certain such embodiments, the non-flowing material can be pre-cooled (e.g., by placement in a refrigerator) prior to the phototherapy treatment to facilitate cooling of the scalp <b>30</b>.

In certain embodiments, the element <b>50</b> is adapted to apply pressure to at least a portion of the scalp <b>30</b>. By applying sufficient pressure, the element <b>50</b> can blanch the portion of the scalp <b>30</b> by forcing at least some blood out the optical path of the light energy. The blood removal resulting from the pressure applied by the element <b>50</b> to the scalp <b>30</b> decreases the corresponding absorption of the light energy by blood in the scalp <b>30</b>. As a result, temperature increases due to absorption of the light energy by blood at the scalp <b>30</b> are reduced. As a further result, the fraction of the light energy transmitted to the subdermal target tissue of the brain <b>20</b> is increased. In certain embodiments, a pressure greater than two pounds per square inch is used to blanch the irradiated portion of the scalp <b>30</b>, while in certain other embodiments, a pressure of at least one pound per square inch is used to blanch the irradiated portion of the scalp <b>30</b>. Other ranges of pressures for blanching the irradiated portion of the scalp <b>30</b> are also compatible with certain embodiments described herein. The maximum pressure used to blanch the irradiated portion of the scalp <b>30</b> is limited in certain embodiments by patient comfort levels and tissue damage levels.

<figref idrefs="DRAWINGS">FIGS. 4A and 4B</figref> schematically illustrate embodiments of the element <b>50</b> adapted to facilitate the blanching of the scalp <b>30</b>. In the cross-sectional view of a portion of the therapy apparatus <b>10</b> schematically illustrated in <figref idrefs="DRAWINGS">FIG. 4A</figref>, certain element portions <b>72</b> contact the patient's scalp <b>30</b> and other element portions <b>74</b> are spaced away from the scalp <b>30</b>. The element portions <b>72</b> contacting the scalp <b>30</b> provide an optical path for light to propagate from the light source <b>40</b> to the scalp <b>30</b>. The element portions <b>72</b> contacting the scalp <b>30</b> also apply pressure to the scalp <b>30</b>, thereby forcing blood out from beneath the element portion <b>72</b>. <figref idrefs="DRAWINGS">FIG. 4B</figref> schematically illustrates a similar view of an embodiment in which the light source <b>40</b> comprises a plurality of light sources <b>40</b><i>a</i>, <b>40</b><i>b</i>, <b>40</b><i>c. </i>

<figref idrefs="DRAWINGS">FIG. 5A</figref> schematically illustrates one embodiment of the cross-section along the line <b>4</b>-<b>4</b> of <figref idrefs="DRAWINGS">FIG. 4B</figref>. The element portions <b>72</b> contacting the scalp <b>30</b> comprise ridges extending along one direction, and the element portions <b>74</b> spaced away from the scalp <b>30</b> comprise troughs extending along the same direction. In certain embodiments, the ridges are substantially parallel to one another and the troughs are substantially parallel to one another. <figref idrefs="DRAWINGS">FIG. 5B</figref> schematically illustrates another embodiment of the cross-section along the line <b>4</b>-<b>4</b> of <figref idrefs="DRAWINGS">FIG. 4B</figref>. The element portions <b>72</b> contacting the scalp <b>30</b> comprise a plurality of projections in the form of a grid or array. More specifically, the portions <b>72</b> are rectangular and are separated by element portions <b>74</b> spaced away from the scalp <b>30</b>, which form troughs extending in two substantially perpendicular directions. The portions <b>72</b> of the element <b>50</b> contacting the scalp <b>30</b> can be a substantial fraction of the total area of the element <b>50</b> or of the scalp <b>30</b>.

<figref idrefs="DRAWINGS">FIGS. 6A-6C</figref> schematically illustrate an embodiment in which the light sources <b>40</b> are spaced away from the scalp <b>30</b>. In certain such embodiments, the light emitted by the light sources <b>40</b> propagates from the light sources <b>40</b> through the scalp <b>30</b> to the brain <b>20</b> and disperses in a direction generally parallel to the scalp <b>30</b>, as shown in <figref idrefs="DRAWINGS">FIG. 6A</figref>. The light sources <b>40</b> are preferably spaced sufficiently far apart from one another such that the light emitted from each light source <b>40</b> overlaps with the light emitted from the neighboring light sources <b>40</b> at the brain <b>20</b>. <figref idrefs="DRAWINGS">FIG. 6B</figref> schematically illustrates this overlap as the overlap of circular spots <b>42</b> at a reference depth at or below the surface of the brain <b>20</b>. <figref idrefs="DRAWINGS">FIG. 6C</figref> schematically illustrates this overlap as a graph of the power density at the reference depth of the brain <b>20</b> along the line L-L of <figref idrefs="DRAWINGS">FIGS. 6A and 6B</figref>. Summing the power densities from the neighboring light sources <b>40</b> (shown as a dashed line in <figref idrefs="DRAWINGS">FIG. 6C</figref>) serves to provide a more uniform light distribution at the tissue to be treated. In such embodiments, the summed power density is preferably less than a damage threshold of the brain <b>20</b> and above an efficacy threshold.

In certain embodiments, the element <b>50</b> is adapted to diffuse the light prior to reaching the scalp <b>30</b>. <figref idrefs="DRAWINGS">FIGS. 7A and 7B</figref> schematically illustrate the diffusive effect on the light by the element <b>50</b>. An example energy density profile of the light emitted by a light source <b>40</b>, as illustrated by <figref idrefs="DRAWINGS">FIG. 7A</figref>, is peaked at a particular emission angle. After being diffused by the element <b>50</b>, as illustrated by <figref idrefs="DRAWINGS">FIG. 7B</figref>, the energy density profile of the light does not have a substantial peak at any particular emission angle, but is substantially evenly distributed among a range of emission angles. By diffusing the light emitted by the light source <b>40</b>, the element <b>50</b> distributes the light energy substantially evenly over the area to be illuminated, thereby inhibiting “hot spots” which would otherwise create temperature increases at the scalp <b>30</b>. In addition, by diffusing the light prior to its reaching the scalp <b>30</b>, the element <b>50</b> can effectively increase the spot size of the light impinging the scalp <b>30</b>, thereby advantageously lowering the power density at the scalp <b>30</b>, as described more fully below. In addition, in embodiments with multiple light sources <b>40</b>, the element <b>50</b> can diffuse the light to alter the total light output distribution to reduce inhomogeneities.

In certain embodiments, the element <b>50</b> provides sufficient diffusion of the light such that the power density of the light is less than a maximum tolerable level of the scalp <b>30</b> and brain <b>20</b>. In certain other embodiments, the element <b>50</b> provides sufficient diffusion of the light such that the power density of the light equals a therapeutic value at the target tissue. The element <b>50</b> can comprise example diffusers including, but are not limited to, holographic diffusers such as those available from Physical Optics Corp. of Torrance, Calif. and Display Optics P/N SN1333 from Reflexite Corp. of Avon, Conn.

Power Density

Phototherapy for the treatment of neurologic conditions (e.g., neurodegenerative diseases such as Parkinson's disease) is based in part on the concept that power density (i.e., power per unit area or number of photons per unit area per unit time) and energy density (i.e., energy per unit area or number of photons per unit area) of the light energy applied to tissue appear to be significant factors in determining the relative efficacy of low level phototherapy. Certain embodiments described herein are based at least in part on the concept that, given a selected wavelength of light energy, it is the power density and/or the energy density of the light delivered to tissue (as opposed to the total power or total energy delivered to the tissue) that are important factors in determining the relative efficacy of phototherapy.

The significance of the power density used in phototherapy has ramifications with regard to the devices and methods used in phototherapy of brain tissue, as schematically illustrated by <figref idrefs="DRAWINGS">FIGS. 8A and 8B</figref>, which show the effects of scattering by intervening tissue. Further information regarding the scattering of light by tissue is provided by V. Tuchin in “Tissue Optics: Light Scattering Methods and Instruments for Medical Diagnosis,” SPIE Press (2000), Bellingham, Wash., pp. 3-11, which is incorporated in its entirety by reference herein.

<figref idrefs="DRAWINGS">FIG. 8A</figref> schematically illustrates a light beam <b>80</b> impinging a portion <b>90</b> of a patient's scalp <b>30</b> and propagating through the patient's head to irradiate a portion <b>100</b> of the patient's brain tissue <b>20</b>. In the example embodiment of <figref idrefs="DRAWINGS">FIG. 8A</figref>, the light beam <b>80</b> impinging the scalp <b>30</b> is collimated and has a circular cross-section with a radius of 2 cm and a cross-sectional area of approximately 12.5 cm². For comparison purposes, <figref idrefs="DRAWINGS">FIG. 8B</figref> schematically illustrates a light beam <b>82</b> having a significantly smaller cross-section impinging a smaller portion <b>92</b> of the scalp <b>30</b> to irradiate a portion <b>102</b> of the brain tissue <b>20</b>. The light beam <b>82</b> impinging the scalp <b>30</b> in <figref idrefs="DRAWINGS">FIG. 8B</figref> is collimated and has a circular cross-section with a radius of 1 cm and a cross-sectional area of approximately 3.1 cm². The collimations, cross-sections, and radii of the light beams <b>80</b>, <b>82</b> illustrated in <figref idrefs="DRAWINGS">FIGS. 8A and 8B</figref> are examples; other light beams with other parameters are also compatible with embodiments described herein. In particular, similar considerations apply to focused beams or diverging beams, as they are similarly scattered by the intervening tissue.

As shown in <figref idrefs="DRAWINGS">FIGS. 8A and 8B</figref>, the cross-sections of the light beams <b>80</b>, <b>82</b> become larger while propagating through the head due to scattering from interactions with tissue of the head. Assuming that the angle of dispersion is 15 degrees and the irradiated brain tissue <b>20</b> is 2.5 cm below the scalp <b>30</b>, the resulting area of the portion <b>100</b> of brain tissue <b>20</b> irradiated by the light beam <b>80</b> in <figref idrefs="DRAWINGS">FIG. 8A</figref> is approximately 22.4 cm². Similarly, the resulting area of the portion <b>102</b> of brain tissue <b>20</b> irradiated by the light beam <b>82</b> in <figref idrefs="DRAWINGS">FIG. 8B</figref> is approximately 8.8 cm².

Irradiating the portion <b>100</b> of the brain tissue <b>20</b> with a power density of 10 mW/cm²corresponds to a total power within the portion <b>100</b> of approximately 224 mW (10 mW/cm²×22.4 cm²). Assuming only approximately 5% of the light beam <b>80</b> is transmitted between the scalp <b>30</b> and the brain tissue <b>20</b>, the incident light beam <b>80</b> at the scalp <b>30</b> will have a total power of approximately 4480 mW (224 mW/0.05) and a power density of approximately 358 mW/cm²(4480 mW/12.5 cm²). Similarly, irradiating the portion <b>102</b> of the brain tissue <b>20</b> with a power density of 10 mW/cm²corresponds to a total power within the portion <b>102</b> of approximately 88 mW (10 mW/cm²×8.8 cm²), and with the same 5% transmittance, the incident light beam <b>82</b> at the scalp <b>30</b> will have a total power of approximately 1760 mW (88 mW/0.05) and a power density of approximately 568 mW/cm²(1760 mW/3.1 cm²). These calculations are summarized in Table 1.

<tables id="TABLE-US-00001" num="00001"><table frame="none" colsep="0" rowsep="0"><tgroup align="left" colsep="0" rowsep="0" cols="3"><colspec colname="offset" colwidth="77pt" align="left" /><colspec colname="1" colwidth="56pt" align="center" /><colspec colname="2" colwidth="84pt" align="center" /><thead><row><entry /><entry namest="offset" nameend="2" rowsep="1">TABLE 1</entry></row><row><entry /><entry namest="offset" nameend="2" align="center" rowsep="1" /></row><row><entry /><entry>2 cm Spot Size</entry><entry>1 cm Spot Size</entry></row><row><entry /><entry>(FIG. 8A)</entry><entry>(FIG. 8B)</entry></row><row><entry /><entry namest="offset" nameend="2" align="center" rowsep="1" /></row></thead><tbody valign="top"><row><entry /></row></tbody></tgroup><tgroup align="left" colsep="0" rowsep="0" cols="6"><colspec colname="offset" colwidth="14pt" align="left" /><colspec colname="1" colwidth="63pt" align="left" /><colspec colname="2" colwidth="21pt" align="right" /><colspec colname="3" colwidth="35pt" align="left" /><colspec colname="4" colwidth="35pt" align="right" /><colspec colname="5" colwidth="49pt" align="left" /><tbody valign="top"><row><entry /><entry>Scalp:</entry><entry /><entry /><entry /><entry /></row><row><entry /><entry>Area</entry><entry>12.5</entry><entry>cm²</entry><entry>3.1</entry><entry>cm²</entry></row><row><entry /><entry>Total power</entry><entry>4480</entry><entry>mW</entry><entry>1760</entry><entry>mW</entry></row><row><entry /><entry>Power density</entry><entry>358</entry><entry>mW/cm²</entry><entry>568</entry><entry>mW/cm²</entry></row><row><entry /><entry>Brain:</entry></row><row><entry /><entry>Area</entry><entry>22.4</entry><entry>cm²</entry><entry>8.8</entry><entry>cm²</entry></row><row><entry /><entry>Total power</entry><entry>224</entry><entry>mW</entry><entry>88</entry><entry>mW</entry></row><row><entry /><entry>Power density</entry><entry>10</entry><entry>mW/cm²</entry><entry>10</entry><entry>mW/cm²</entry></row><row><entry /><entry namest="offset" nameend="5" align="center" rowsep="1" /></row></tbody></tgroup></table></tables>

These example calculations illustrate that to obtain a desired power density at the brain <b>20</b>, higher total power at the scalp <b>30</b> can be used in conjunction with a larger spot size at the scalp <b>30</b>. Thus, by increasing the spot size at the scalp <b>30</b>, a desired power density at the brain <b>20</b> can be achieved with lower power densities at the scalp <b>30</b> which can reduce the possibility of overheating the scalp <b>30</b>. In certain embodiments, the light can be directed through an aperture to define the illumination of the scalp <b>30</b> to a selected smaller area.

Light Source

In certain embodiments, a single light source <b>40</b> is used as a light generator to generate light, while in other embodiments, a plurality of light sources <b>40</b> are used as a light generator to generate light. The light source <b>40</b> preferably generates light in the visible to near-infrared wavelength range. In certain embodiments, the light source <b>40</b> comprises one or more laser diodes, which each provide coherent light. In embodiments in which the light from the light source <b>40</b> is coherent, the emitted light may produce “speckling” due to coherent interference of the light. This speckling comprises intensity spikes which are created by constructive interference and can occur in proximity to the target tissue being treated. For example, while the average power density may be approximately 10 mW/cm², the power density of one such intensity spike in proximity to the brain tissue to be treated may be approximately 300 mW/cm². In certain embodiments, this increased power density due to speckling can improve the efficacy of treatments using coherent light over those using incoherent light for illumination of deeper tissues.

In other embodiments, the light source <b>40</b> provides incoherent light. Example light sources <b>40</b> of incoherent light include, but are not limited to, incandescent lamps or light-emitting diodes. A heat sink can be used with the light source <b>40</b> (for either coherent or incoherent sources) to remove heat from the light source <b>40</b> and to inhibit temperature increases at the scalp <b>30</b>.

In certain embodiments, the light source <b>40</b> generates light which is substantially monochromatic (i.e., light having one wavelength, or light having a narrow band of wavelengths). So that the amount of light transmitted to the brain is maximized, the wavelength of the light is selected in certain embodiments to be at or near a transmission peak (or at or near an absorption minimum) for the intervening tissue. In certain such embodiments, the wavelength corresponds to a peak in the transmission spectrum of tissue at about 820 nanometers. In other embodiments, the wavelength of the light is preferably between about 630 nanometers and about 1064 nanometers, more preferably between about 780 nanometers and about 840 nanometers, and most preferably includes wavelengths of about 785, 790, 795, 800, 805, 810, 815, 820, 825, or 830 nanometers. An intermediate wavelength in a range between approximately 730 nanometers and approximately 750 nanometers (e.g., about 739 nanometers) appears to be suitable for penetrating the skull, although other wavelengths are also suitable and may be used.

In other embodiments, the light source <b>40</b> generates light having a plurality of wavelengths. For example, in certain embodiments, a band of wavelengths of (808±5) nanometers is used. In certain embodiments, the light source <b>40</b> is adapted to generate light having a first wavelength concurrently with light having a second wavelength. In certain other embodiments, the light source <b>40</b> is adapted to generate light having a first wavelength sequentially with light having a second wavelength.

In certain such embodiments, each wavelength is selected so as to work with one or more chromophores within the target tissue. Without being bound by theory or by a specific mechanism, it is believed that irradiation of chromophores increases the production of ATP in the target tissue, thereby producing beneficial effects, as described more fully below.

In certain embodiments, the light source <b>40</b> includes at least one continuously emitting GaAlAs laser diode having a wavelength of about 830 nanometers. In another embodiment, the light source <b>40</b> comprises a laser source having a wavelength of about 808 nanometers. In still other embodiments, the light source <b>40</b> includes at least one vertical cavity surface-emitting laser (VCSEL) diode. Other light sources <b>40</b> compatible with embodiments described herein include, but are not limited to, light-emitting diodes (LEDs) and filtered lamps.

The light source <b>40</b> is capable of emitting light energy at a power sufficient to achieve a predetermined power density at the subdermal target tissue (e.g., at a depth of approximately 2 centimeters from the dura). It is presently believed that phototherapy of tissue is most effective when irradiating the target tissue with power densities of light of at least about 0.01 mW/cm²and up to about 1 W/cm²at the level of the tissue. In various embodiments, the subsurface power density is at least about 0.01, 0.05, 0.1, 0.5, 1, 5, 10, 15, 20, 30, 40, 50, 60, 70, 80, or 90 mW/cm², respectively, depending on the desired clinical performance. In certain embodiments, the subsurface power density at the target tissue is about 0.01 mW/cm²to about 100 mW/cm², about 0.01 mW/cm²to about 50 mW/cm², about 2 mW/cm²to about 20 mW/cm², or about 5 mW/cm²to about 25 mW/cm². It is believed that these subsurface power densities are especially effective at producing the desired biostimulative effects on the tissue being treated.

Taking into account the attenuation of energy as it propagates from the skin surface, through body tissue, bone, and fluids, to the subdermal target tissue, surface power densities preferably between about 10 mW/cm²to about 10 W/cm², or more preferably between about 100 mW/cm²to about 500 mW/cm², will typically be used to attain the selected power densities at the subdermal target tissue. To achieve such surface power densities, the light source <b>40</b> is preferably capable of emitting light energy having a total power output of at least about 25 mW to about 100 W. In various embodiments, the total power output is limited to be no more than about 30, 50, 75, 100, 150, 200, 250, 300, 400, or 500 mW, respectively. In certain embodiments, the light source <b>40</b> comprises a plurality of sources used in combination to provide the total power output. The actual power output of the light source <b>40</b> is preferably controllably variable. In this way, the power of the light energy emitted can be adjusted in accordance with a selected power density at the subdermal tissue being treated.

Certain embodiments utilize a light source <b>40</b> that includes only a single laser diode that is capable of providing about 25 mW to about 100 W of total power output at the skin surface. In certain such embodiments, the laser diode can be optically coupled to the scalp <b>30</b> via an optical fiber or can be configured to provide a sufficiently large spot size to avoid power densities which would burn or otherwise damage the scalp <b>30</b>. In other embodiments, the light source <b>40</b> utilizes a plurality of sources (e.g., laser diodes) arranged in a grid or array that together are capable of providing at least about 25 mW to about 100 W of total power output at the skin surface. The light source <b>40</b> of other embodiments may also comprise sources having power capacities outside of these limits.

<figref idrefs="DRAWINGS">FIG. 9A</figref> schematically illustrates another embodiment of the therapy apparatus <b>10</b> which comprises the cap <b>60</b> and a light source comprising a light-emitting blanket <b>110</b>. <figref idrefs="DRAWINGS">FIG. 9B</figref> schematically illustrates an embodiment of the blanket <b>110</b> comprising a flexible substrate <b>111</b> (e.g., flexible circuit board), a power conduit interface <b>112</b>, and a sheet formed by optical fibers <b>114</b> positioned in a fan-like configuration. <figref idrefs="DRAWINGS">FIG. 9C</figref> schematically illustrates an embodiment of the blanket <b>110</b> comprising a flexible substrate <b>111</b>, a power conduit interface <b>112</b>, and a sheet formed by optical fibers <b>114</b> woven into a mesh. The blanket <b>110</b> is preferably positioned within the cap <b>60</b> so as to cover an area of the scalp <b>30</b> corresponding to a portion of the brain <b>20</b> to be treated.

In certain such embodiments, the power conduit interface <b>112</b> is adapted to be coupled to an optical fiber conduit <b>64</b> which provides optical power to the blanket <b>110</b>. The optical power interface <b>112</b> of certain embodiments comprises a beam splitter or other optical device which distributes the incoming optical power among the various optical fibers <b>114</b>. In other embodiments, the power conduit interface <b>112</b> is adapted to be coupled to an electrical conduit which provides electrical power to the blanket <b>110</b>. In certain such embodiments, the power conduit interface <b>112</b> comprises one or more laser diodes, the output of which is distributed among the various optical fibers <b>114</b> of the blanket <b>110</b>. In certain other embodiments, the blanket <b>110</b> comprises an electroluminescent sheet which responds to electrical signals from the power conduit interface <b>112</b> by emitting light. In such embodiments, the power conduit interface <b>112</b> comprises circuitry adapted to distribute the electrical signals to appropriate portions of the electroluminescent sheet.

The side of the blanket <b>110</b> nearer the scalp <b>30</b> is preferably provided with a light scattering surface, such as a roughened surface to increase the amount of light scattered out of the blanket <b>110</b> towards the scalp <b>30</b>. The side of the blanket <b>110</b> further from the scalp <b>30</b> is preferably covered by a reflective coating so that light emitted away from the scalp <b>30</b> is reflected back towards the scalp <b>30</b>. This configuration is similar to configurations used for the “back illumination” of liquid-crystal displays (LCDs). Other configurations of the blanket <b>110</b> are compatible with embodiments described herein.

In certain embodiments, the light source <b>40</b> generates light which cause eye damage if viewed by an individual. In such embodiments, the apparatus <b>50</b> can be configured to provide eye protection so as to avoid viewing of the light by individuals. For example, opaque materials can be appropriately placed to block the light from being viewed directly. In addition, interlocks can be provided so that the light source <b>40</b> is not activated unless the apparatus <b>50</b> is in place, or other appropriate safety measures are taken.

Light Delivery Apparatuses

The phototherapy methods for the treatments described herein may be practiced and described using, for example, a low level laser therapy apparatus such as that shown and described in U.S. Pat. No. 6,214,035, U.S. Pat. No. 6,267,780, U.S. Pat. No. 6,273,905 and U.S. Pat. No. 6,290,714, which are all incorporated in their entirety by reference herein, as are the references incorporated by reference therein.

Another suitable phototherapy apparatus in accordance with embodiments described here is illustrated in <figref idrefs="DRAWINGS">FIG. 10</figref>. The illustrated therapy apparatus <b>10</b> includes a light source <b>40</b>, an element <b>50</b>, and a flexible strap <b>120</b> adapted for securing the therapy apparatus <b>10</b> over an area of the patient's head. The light source <b>40</b> can be disposed on the strap <b>120</b> itself, or in a housing <b>122</b> coupled to the strap <b>120</b>. The light source <b>40</b> preferably comprises a plurality of diodes <b>40</b><i>a</i>, <b>40</b><i>b</i>, etc. capable of emitting light energy having a wavelength in the visible to near-infrared wavelength range. The element <b>50</b> is adapted to be positioned between the light source <b>40</b> and the patient's scalp <b>30</b>.

The therapy apparatus <b>10</b> further includes a power supply (not shown) operatively coupled to the light source <b>40</b>, and a programmable controller <b>126</b> operatively coupled to the light source <b>40</b> and to the power supply. The programmable controller <b>126</b> is configured to control the light source <b>40</b> so as to deliver a predetermined power density to the brain tissue <b>20</b>. In certain embodiments, as schematically illustrated in <figref idrefs="DRAWINGS">FIG. 10</figref>, the light source <b>40</b> comprises the programmable controller <b>126</b>. In other embodiments the programmable controller <b>126</b> is a separate component of the therapy apparatus <b>10</b>.

In certain embodiments, the strap <b>120</b> comprises a loop of elastomeric material sized appropriately to fit snugly onto the patient's scalp <b>30</b>. In other embodiments, the strap <b>120</b> comprises an elastomeric material to which is secured any suitable securing means <b>130</b>, such as mating Velcro strips, buckles, snaps, hooks, buttons, ties, or the like. The precise configuration of the strap <b>120</b> is subject only to the limitation that the strap <b>120</b> is capable of maintaining the light source <b>40</b> in a selected position so that light energy emitted by the light source <b>40</b> is directed towards the targeted brain tissue <b>20</b>.

In the example embodiment illustrated in <figref idrefs="DRAWINGS">FIG. 10</figref>, the housing <b>122</b> comprises a layer of flexible plastic or fabric that is secured to the strap <b>120</b>. In other embodiments, the housing <b>122</b> comprises a plate or an enlarged portion of the strap <b>120</b>. Various strap configurations and spatial distributions of the light sources <b>40</b> are compatible with embodiments described herein so that the therapy apparatus <b>10</b> can treat selected portions of brain tissue.

In still other embodiments, the therapy apparatus <b>10</b> for delivering the light energy includes a handheld probe <b>140</b>, as schematically illustrated in <figref idrefs="DRAWINGS">FIG. 11</figref>. The probe <b>140</b> includes a light source <b>40</b> and an element <b>50</b> as described herein.

<figref idrefs="DRAWINGS">FIG. 12</figref> is a block diagram of a control circuit <b>200</b> comprising a programmable controller <b>126</b> according to embodiments described herein. The control circuit <b>200</b> is configured to adjust the power of the light energy emitted by the light source <b>40</b> to generate a predetermined surface power density at the scalp <b>30</b> corresponding to a predetermined energy delivery profile, such as a predetermined subsurface power density, to the target area of the brain <b>20</b>.

In certain embodiments, the programmable controller <b>126</b> comprises a logic circuit <b>210</b>, a clock <b>212</b> coupled to the logic circuit <b>210</b>, and an interface <b>214</b> coupled to the logic circuit <b>210</b>. The clock <b>212</b> of certain embodiments provides a timing signal to the logic circuit <b>210</b> so that the logic circuit <b>210</b> can monitor and control timing intervals of the applied light. Examples of timing intervals include, but are not limited to, total treatment times, pulsewidth times for pulses of applied light, and time intervals between pulses of applied light. In certain embodiments, the light sources <b>40</b> can be selectively turned on and off to reduce the thermal load on the scalp <b>30</b> and to deliver a selected power density to particular areas of the brain <b>20</b>.

The interface <b>214</b> of certain embodiments provides signals to the logic circuit <b>210</b> which the logic circuit <b>210</b> uses to control the applied light. The interface <b>214</b> can comprise a user interface or an interface to a sensor monitoring at least one parameter of the treatment. In certain such embodiments, the programmable controller <b>126</b> is responsive to signals from the sensor to preferably adjust the treatment parameters to optimize the measured response. The programmable controller <b>126</b> can thus provide closed-loop monitoring and adjustment of various treatment parameters to optimize the phototherapy. The signals provided by the interface <b>214</b> from a user are indicative of parameters that may include, but are not limited to, patient characteristics (e.g., skin type, fat percentage), selected applied power densities, target time intervals, and power density/timing profiles for the applied light.

In certain embodiments, the logic circuit <b>210</b> is coupled to a light source driver <b>220</b>. The light source driver <b>220</b> is coupled to a power supply <b>230</b>, which in certain embodiments comprises a battery and in other embodiments comprises an alternating current source. The light source driver <b>220</b> is also coupled to the light source <b>40</b>. The logic circuit <b>210</b> is responsive to the signal from the clock <b>212</b> and to user input from the user interface <b>214</b> to transmit a control signal to the light source driver <b>220</b>. In response to the control signal from the logic circuit <b>210</b>, the light source driver <b>220</b> adjust and controls the power applied to the light sources <b>40</b>. Other control circuits besides the control circuit <b>200</b> of <figref idrefs="DRAWINGS">FIG. 12</figref> are compatible with embodiments described herein.

In certain embodiments, the logic circuit <b>110</b> is responsive to signals from a sensor monitoring at least one parameter of the treatment to control the applied light. For example, certain embodiments comprise a temperature sensor thermally coupled to the scalp <b>30</b> to provide information regarding the temperature of the scalp <b>30</b> to the logic circuit <b>210</b>. In such embodiments, the logic circuit <b>210</b> is responsive to the information from the temperature sensor to transmit a control signal to the light source driver <b>220</b> so as to adjust the parameters of the applied light to maintain the scalp temperature below a predetermined level. Other embodiments include example biomedical sensors including, but not limited to, a blood flow sensor, a blood gas (e.g., oxygenation) sensor, an ATP production sensor, or a cellular activity sensor. Such biomedical sensors can provide real-time feedback information to the logic circuit <b>210</b>. In certain such embodiments, the logic circuit <b>110</b> is responsive to signals from the sensors to preferably adjust the parameters of the applied light to optimize the measured response. The logic circuit <b>110</b> can thus provide closed-loop monitoring and adjustment of various parameters of the applied light to optimize the phototherapy.

In certain embodiments, as schematically illustrated in <figref idrefs="DRAWINGS">FIG. 13</figref>, the therapy apparatus <b>310</b> comprises a light source <b>340</b> adapted to irradiate a portion of the patient's brain <b>20</b> with an efficacious power density and wavelength of light. The therapy apparatus <b>310</b> further comprises a controller <b>360</b> for energizing said light source <b>340</b>, so as to selectively produce a plurality of different irradiation patterns on the patient's scalp <b>30</b>. Each of the irradiation patterns is comprised of a least one illuminated area that is small compared to the patient's scalp <b>30</b>, and at least one non-illuminated area.

In certain embodiments, the light source <b>340</b> includes an apparatus for adjusting the emitted light to irradiate different portions of the scalp <b>30</b>. In certain such embodiments, the apparatus physically moves the light source <b>40</b> relative to the scalp <b>30</b>. In other embodiments, the apparatus does not move the light source <b>40</b>, but redirects the emitted light to different portions of the scalp <b>30</b>. In an example embodiment, as schematically illustrated in <figref idrefs="DRAWINGS">FIG. 14</figref>, the light source <b>340</b> comprises a laser diode <b>342</b> and a galvometer <b>344</b>, both of which are electrically coupled to the controller <b>360</b>. The galvometer <b>344</b> comprises a mirror <b>346</b> mounted onto an assembly <b>348</b> which is adjustable by a plurality of motors <b>350</b>. Light emitted by the laser diode <b>342</b> is directed toward the mirror <b>346</b> and is reflected to selected portions of the patient's scalp <b>30</b> by selectively moving the mirror <b>346</b> and selectively activating the laser diode <b>342</b>. In certain embodiments, the therapy apparatus <b>310</b> comprises an element <b>50</b> adapted to inhibit temperature increases at the scalp <b>30</b> as described herein.

<figref idrefs="DRAWINGS">FIG. 15A</figref> schematically illustrates an irradiation pattern <b>370</b> in accordance with embodiments described herein. The irradiation pattern <b>370</b> comprises at least one illuminated area <b>372</b> and at least one non-illuminated area <b>374</b>. In certain embodiments, the irradiation pattern <b>370</b> is generated by scanning the mirror <b>346</b> so that the light impinges the patient's scalp <b>30</b> in the illuminated area <b>372</b> but not in the non-illuminated area <b>374</b>. Certain embodiments modify the illuminated area <b>372</b> and the non-illuminated area <b>374</b> as a function of time.

This selective irradiation can be used to reduce the thermal load on particular locations of the scalp <b>30</b> by moving the light from one illuminated area <b>372</b> to another. For example, by irradiating the scalp <b>30</b> with the irradiation pattern <b>370</b> schematically illustrated in <figref idrefs="DRAWINGS">FIG. 15A</figref>, the illuminated areas <b>372</b> of the scalp <b>30</b> are heated by interaction with the light, and the non-illuminated areas <b>374</b> are not heated. By subsequently irradiating the scalp <b>30</b> with the complementary irradiation pattern <b>370</b>′ schematically illustrated in <figref idrefs="DRAWINGS">FIG. 15B</figref>, the previously non-illuminated areas <b>374</b> are now illuminated areas <b>372</b>′, and the previously illuminated areas <b>372</b> are now non-illuminated areas <b>374</b>′. A comparison of the illuminated areas <b>372</b> of the irradiation pattern <b>370</b> of <figref idrefs="DRAWINGS">FIG. 15A</figref> with the illuminated area <b>372</b>′ of the irradiation pattern <b>370</b>′ of <figref idrefs="DRAWINGS">FIG. 15B</figref> shows that the illuminated areas <b>372</b>, <b>372</b>′ do not significantly overlap one another. In this way, the thermal load at the scalp <b>30</b> due to the absorption of the light can be distributed across the scalp <b>30</b>, thereby avoiding unduly heating one or more portions of the scalp <b>30</b>.

<figref idrefs="DRAWINGS">FIG. 16</figref> schematically illustrates another therapy apparatus <b>400</b> in accordance with embodiments described herein. The therapy apparatus <b>400</b> comprises a plurality of light sources <b>410</b> in a housing <b>420</b>. Each light source <b>410</b> has an output emission area positioned to irradiate a corresponding portion of the brain <b>20</b> with an efficacious power density and wavelength of light. In certain embodiments, these portions overlap such that the portion of the brain <b>20</b> irradiated by two or more light sources <b>410</b> overlap one another at least in part. As described herein, the light sources <b>410</b> can be activated by a controller (not shown) in concert or separately to produce a predetermined irradiation pattern.

The therapy apparatus <b>400</b> of <figref idrefs="DRAWINGS">FIG. 16</figref> further comprises a cap <b>430</b> interposed between the light sources <b>410</b> and the patient's scalp <b>30</b>, such that light passes through the cap <b>430</b> prior to reaching the scalp <b>30</b>. In certain embodiments, the cap <b>430</b> is substantially optically transmissive at the wavelength and reduces back reflections of the light. The cap <b>430</b> of certain embodiments fits to the scalp <b>30</b> so as to substantially reduce air gaps between the scalp <b>30</b> and the cap <b>430</b>. In certain embodiments, the cap <b>430</b> comprises a material having a refractive index which substantially matches a refractive index of the scalp <b>30</b>. In certain embodiments, the cap <b>430</b> comprises a material having a refractive index which substantially matches a refractive index of the skin and/or hair of the scalp <b>30</b>.

In the embodiment schematically illustrated by <figref idrefs="DRAWINGS">FIG. 16</figref>, the cap <b>430</b> is wearable over the patient's scalp <b>30</b>. In certain such embodiments, the patient wears the cap <b>430</b> and is in a reclining position so as to place his head in proximity to the light sources <b>410</b>. The cap <b>430</b> is adapted to inhibit temperature increases at the scalp <b>30</b> caused by the light from the light sources <b>410</b>, as described herein (e.g., by cooling the scalp <b>30</b>, by blanching a portion of the scalp <b>30</b>, by diffusing the light prior to reaching the scalp <b>30</b>).

Example Wearable Apparatus

<figref idrefs="DRAWINGS">FIG. 19</figref> schematically illustrates an example apparatus <b>500</b> which is wearable by a patient for treating the patient's brain. The apparatus <b>500</b> comprises a body <b>510</b> and a plurality of elements <b>520</b>. The body <b>510</b> covers at least a portion of the patient's scalp when the apparatus <b>500</b> is worn by the patient. Each element <b>520</b> has a first portion <b>522</b> which conforms to a corresponding portion of the patient's scalp when the apparatus <b>500</b> is worn by the patient. Each element <b>520</b> has a second portion <b>524</b> which conforms to a light source (not shown in <figref idrefs="DRAWINGS">FIG. 19</figref>) removably contacting the element. Each element <b>520</b> is substantially transmissive (e.g., substantially transparent or substantially translucent) to light from the light source to irradiate at least a portion of the patient's brain. In certain embodiments, the light from the light source after being transmitted through each element <b>520</b> has a power density which penetrates the patient's cranium to deliver an efficacious amount of light to at least a portion of the patient's brain.

<figref idrefs="DRAWINGS">FIG. 20</figref> schematically illustrates an example apparatus <b>500</b> having a plurality of elements <b>520</b> in accordance with certain embodiments described herein. The body <b>510</b> shown in <figref idrefs="DRAWINGS">FIG. 20</figref> has a plurality of apertures <b>512</b> or openings which serve as indicators of treatment site locations. Each element <b>520</b> is positioned at a corresponding one of the plurality of apertures <b>512</b> and serves as an optical window. In certain embodiments, the plurality of elements <b>520</b> comprises at least about 10 elements <b>520</b>, while in certain other embodiments, the plurality of elements <b>520</b> comprises 20 elements <b>520</b>. In certain other embodiments, the plurality of elements <b>520</b> comprises between 15 and 25 elements <b>520</b>. In certain embodiments in which the light emitting apparatus <b>600</b> is configured to directly contact the scalp, the apertures <b>512</b> of the body <b>510</b> do not contain any elements <b>520</b>, but instead are indicators of treatment site locations through which the light emitting apparatus <b>600</b> is positioned for treatment.

In certain embodiments, the body <b>510</b> comprises a hood, as schematically illustrated by <figref idrefs="DRAWINGS">FIG. 20</figref>, while in other embodiments, the body <b>510</b> comprises a cap or has another configuration which is wearable on the patient's head and serves as a support for orienting the elements <b>520</b> on the patient's head. In certain embodiments, the body <b>510</b> comprises a stretchable material which generally conforms to the patient's scalp. In certain embodiments, the body <b>510</b> comprises nylon-backed polychloroprene. In certain embodiments, the body <b>510</b> is available in different sizes (e.g., small, medium, large) to accommodate different sizes of heads. In certain embodiments, the apparatus <b>500</b> is disposable after a single use to advantageously avoid spreading infection or disease between subsequent patients.

<figref idrefs="DRAWINGS">FIG. 21</figref> schematically illustrates an example element <b>520</b> in an exploded view. The example element <b>520</b> comprises an optical component <b>532</b>, a first support ring <b>534</b>, a second support ring <b>536</b>, and a label <b>538</b>. Other configurations of the element <b>520</b> are also compatible with certain embodiments described herein.

In certain embodiments, the optical component <b>532</b> comprises a substantially transmissive (e.g., substantially transparent or substantially translucent) bag comprising a flexible material (which can be biocompatible). <figref idrefs="DRAWINGS">FIG. 22A</figref> schematically illustrates an example optical component <b>532</b> with example dimensions in inches. The bag of <figref idrefs="DRAWINGS">FIG. 22A</figref> comprises an inflatable container which contains a substantially transmissive liquid (e.g., water) or gel. In certain embodiments, the bag has an outer diameter within a range between about 0.5 inch and about 3 inches. For example, the bag of <figref idrefs="DRAWINGS">FIG. 22A</figref> has an outer diameter of about 1.37 inches. In certain embodiments, the bag has a volume in a range between about 2 cubic centimeters and about 50 cubic centimeters.

Both the bag and the liquid contained within the bag are substantially transmissive to light having wavelengths to be applied to the patient's brain (e.g., wavelength of approximately 810 nanometers). In certain embodiments, the liquid has a refractive index which substantially matches a refractive index of the patient's scalp, thereby advantageously providing an optical match between the element <b>520</b> and the patient's scalp. While the example optical component <b>532</b> of <figref idrefs="DRAWINGS">FIG. 22A</figref> comprises a single bag, in certain other embodiments, the optical component <b>532</b> comprises a plurality of bags filled with a substantially transparent liquid.

<figref idrefs="DRAWINGS">FIGS. 22B and 22C</figref> schematically illustrate other example optical components <b>532</b> in which the bag contains a composite material. For example, in <figref idrefs="DRAWINGS">FIGS. 22B and 22C</figref>, the bag contains a first material <b>523</b> and a second material <b>525</b>. In certain embodiments, the first material <b>523</b> comprises a soft, substantially transmissive, thermally insulative material (e.g., gel). Example gels compatible with certain embodiments described herein include, but are not limited to, OC-431A-LVP, OCK-451, and OC-462 optical gels available from Nye Corporation of Fairhaven, Mass. In certain embodiments, the second material <b>525</b> comprises a rigid, substantially transmissive, thermally conductive material (e.g., silica).

In certain embodiments, as schematically illustrated in <figref idrefs="DRAWINGS">FIG. 22B</figref>, the second material <b>525</b> comprises a plurality of balls distributed within the first material <b>523</b>. The balls of certain embodiments have diameters less than about 2 millimeters. In certain other embodiments, as schematically illustrated in <figref idrefs="DRAWINGS">FIG. 22C</figref>, the first material <b>523</b> comprises a first plurality of layers and the second material <b>525</b> comprises a second plurality of layers. The first plurality of layers is stacked with the second plurality of layers, thereby forming a stack having alternating layers of the first material <b>523</b> and the second material <b>525</b>. In certain embodiments, each layer of the first plurality of layers has a thickness less than about 2 millimeters and each layer of the second plurality of layers has a thickness less than about 2 millimeters. In certain other embodiments, each layer of the first plurality of layers and each layer of the second plurality of layers has a thickness less than about 0.5 millimeter. Other configurations of the first material <b>523</b> and the second material <b>525</b> within the optical component <b>532</b> are also compatible with certain embodiments described herein.

The optical component <b>532</b> of certain embodiments advantageously deforms in response to pressure applied to the first portion <b>522</b> and the second portion <b>524</b>. For example, without a load being applied, the optical component <b>532</b> of <figref idrefs="DRAWINGS">FIG. 22A</figref> has a thickness of approximately 0.41 inch, but with approximately four pounds of applied pressure, the optical component <b>532</b> of <figref idrefs="DRAWINGS">FIG. 22A</figref> has a thickness of approximately 0.315 inch. The first portion <b>522</b> of the optical component <b>532</b> advantageously deforms to substantially conform to a portion of the patient's skull to which the optical component <b>532</b> is pressed. For example, in certain embodiments, the first portion <b>522</b> comprises a conformable surface of the optical component <b>532</b>. Thus, in certain such embodiments, the optical component <b>532</b> advantageously provides an interface with the patient's scalp which is substantially free of air gaps. The second portion <b>524</b> of the optical component <b>532</b> advantageously deforms to substantially conform to a light source being pressed thereon. For example, in certain embodiments, the second portion <b>524</b> comprises a conformable surface of the optical component <b>532</b>. Thus, in certain such embodiments, the optical component <b>532</b> advantageously provides an interface with the light source which is substantially free of air gaps.

In certain embodiments, the optical component <b>532</b> advantageously serves as a heat sink to inhibit temperature increases at the patient's scalp caused by light which is transmitted through the optical component <b>532</b>. In certain such embodiments, the optical component <b>532</b> has a sufficiently high heat capacity to provide an effective heat sink to the patient's scalp. For example, for a bag filled with water (which has a heat capacity of approximately 4180 joules/kilogram-K), a generally disk-shaped bag having a diameter of approximately 32 millimeters and a thickness of approximately 10 millimeters has a sufficient volume, and a sufficient heat capacity, to provide an effective heat sink. Thus, in certain embodiments, each element <b>520</b> advantageously inhibits temperature increases at the patient's scalp caused by the light transmitted through the element <b>520</b>.

<figref idrefs="DRAWINGS">FIG. 23</figref> schematically illustrates an example first support ring <b>534</b> with example dimensions in inches. In certain embodiments, the first support ring <b>534</b> comprises a substantially rigid material. Examples of compatible materials include, but are not limited to, plastic (e.g., acrylonitrile butadiene styrene or ABS). As illustrated in <figref idrefs="DRAWINGS">FIG. 23</figref>, the first support ring <b>534</b> of certain embodiments is configured to be mounted in a corresponding aperture <b>512</b> of the body <b>510</b>. The example first support ring <b>534</b> illustrated in <figref idrefs="DRAWINGS">FIG. 23</figref> comprises a generally flat portion <b>542</b>, an annular portion <b>544</b>, and one or more protrusions <b>546</b> configured to connect to the second support ring <b>536</b>, described more fully below. The generally flat portion <b>542</b> has an outer diameter which is larger than the diameter of the corresponding aperture <b>512</b> of the body <b>510</b> and is configured to be mechanically coupled to the body <b>510</b> (e.g., by adhesive). The annular portion <b>544</b> has an outer diameter which is smaller than or equal to the diameter of the corresponding aperture <b>512</b> of the body <b>510</b> and is configured to fit through the aperture <b>512</b>. The one or more protrusions <b>546</b> extend generally radially from the annular portion <b>544</b> such that the overall width of the protrusions <b>546</b> and the annular portion <b>544</b> is larger than the diameter of the corresponding aperture <b>512</b> of the body <b>510</b>.

<figref idrefs="DRAWINGS">FIG. 24</figref> schematically illustrates an example second support ring <b>536</b> with example dimensions in inches. In certain embodiments, the second support ring <b>536</b> comprises a substantially rigid material. Examples of compatible materials include, but are not limited to, plastic (e.g., acrylonitrile butadiene styrene or ABS). As illustrated in <figref idrefs="DRAWINGS">FIG. 24</figref>, the second support ring <b>536</b> of certain embodiments is configured to be connected to the one or more protrusions <b>546</b> and the annular portion <b>544</b> of the first support ring <b>534</b>. In certain embodiments, the second support ring <b>536</b> comprises one or more recesses (not shown) which are configured to fit with the one or more protrusions <b>546</b> of the first support ring <b>534</b>. In certain such embodiments, the first support ring <b>534</b> and the second support ring <b>536</b> interlock together to advantageously hold the element <b>520</b> in place on the body <b>510</b>. In certain other embodiments, the first support ring <b>534</b> comprises one or more recesses configured to mate with one or more corresponding protrusions of the second support ring <b>536</b>.

<figref idrefs="DRAWINGS">FIG. 25</figref> schematically illustrates an example label <b>538</b> compatible with certain embodiments described herein. The labels <b>538</b> advantageously provide one or more numbers, letters, or symbols (e.g., bar codes) to each of the elements <b>520</b> to distinguish the various elements <b>520</b> from one another. In certain such embodiments, the labels <b>538</b> comprise a vinyl material and are mechanically coupled to the second support ring <b>536</b> (e.g., by adhesive) so as to be visible to users of the light therapy apparatus. Other types of labels <b>538</b> are also compatible with embodiments disclosed herein, including but not limited to, labels <b>538</b> which are painted or etched onto an outside surface of the second support ring <b>536</b>.

<figref idrefs="DRAWINGS">FIGS. 26A and 26B</figref> schematically illustrate the left-side and right-side of the apparatus <b>500</b>, respectively, showing an example labeling configuration for the apparatus <b>500</b>. <figref idrefs="DRAWINGS">FIG. 26C</figref> schematically illustrates the example labeling configuration of <figref idrefs="DRAWINGS">FIGS. 26A and 26B</figref> from above a flattened view of the apparatus <b>500</b>. The labeling convention of <figref idrefs="DRAWINGS">FIGS. 26A-26C</figref> is compatible with irradiation of both halves of the patient's brain. Other labeling conventions are also compatible with embodiments described herein.

In certain embodiments, the labels <b>538</b> are advantageously used to guide an operator to irradiate the patient's brain at the various treatment sites sequentially at each of the treatment sites one at a time through the elements <b>520</b> in a predetermined order using a light source which can be optically coupled to sequential elements <b>520</b>. For example, for the labeling configuration of <figref idrefs="DRAWINGS">FIGS. 26A-26C</figref>, the operator can first irradiate element “1,” followed by elements “2,” “3,”, “4,” etc. to sequentially irradiate each of the twenty treatment sites one at a time. In certain such embodiments, the order of the elements <b>520</b> is selected to advantageously reduce temperature increases which would result from sequentially irradiating elements <b>520</b> in proximity to one another.

In certain embodiments, the labels <b>538</b> are advantageously used to keep track of which elements <b>520</b> have been irradiated and which elements <b>520</b> are yet to be irradiated. In certain such embodiments, at least a portion of each label <b>538</b> (e.g., a pull-off tab) is configured to be removed from the apparatus <b>500</b> when the corresponding element <b>520</b> has been irradiated. In certain embodiments, the label <b>538</b> has a code sequence which the operator enters into the controller prior to irradiation so as to inform the controller of which element <b>520</b> is next to be irradiated. In certain other embodiments, each label <b>538</b> comprises a bar code or a radio-frequency identification device (RFID) which is readable by a sensor electrically coupled to the controller. The controller of such embodiments keeps track of which elements <b>520</b> have been irradiated, and in certain such embodiments, the controller only actuates the light source when the light source is optically coupled to the proper element <b>520</b>.

<figref idrefs="DRAWINGS">FIGS. 27A-27E</figref> schematically illustrate various stages of structures formed during the fabrication of the apparatus <b>500</b> of <figref idrefs="DRAWINGS">FIGS. 20-25</figref>. <figref idrefs="DRAWINGS">FIG. 27A</figref> schematically illustrates the body <b>510</b> mounted on a mannequin head fixture <b>560</b>. The body <b>510</b> is mounted in an inside-out configuration and is shown in <figref idrefs="DRAWINGS">FIG. 27A</figref> after each of the apertures <b>512</b> has been cut in the body <b>510</b>. In each of the apertures <b>512</b>, a first support ring <b>534</b> is connected to the body <b>510</b>, as shown in <figref idrefs="DRAWINGS">FIG. 27B</figref>. In certain embodiments, a layer of adhesive (e.g., CA40 Scotch-Weld™ instant adhesive available from 3M Company of Saint Paul, Minn.) is applied to a surface of the flat portion <b>542</b> which is then pressed onto the body <b>510</b> with the annular portion <b>544</b> extending through the aperture <b>512</b>. <figref idrefs="DRAWINGS">FIG. 27C</figref> schematically illustrates the optical components <b>532</b> mounted on each of the first support rings <b>534</b>. In certain embodiments, a layer of adhesive (e.g., Loctite® 3105 ultraviolet-cured adhesive available from Henkel Corporation of Rocky Hill, Conn.) is applied to a surface of the flat portion <b>542</b> which is then pressed together with a corresponding surface of the optical component <b>532</b> and the adhesive is cured by application of ultraviolet light. <figref idrefs="DRAWINGS">FIG. 27D</figref> schematically illustrates the body <b>510</b> after being removed from the mannequin head fixture <b>560</b> and returned to an right-side-out configuration. <figref idrefs="DRAWINGS">FIG. 27E</figref> schematically illustrates the apparatus <b>500</b> after the second support rings <b>536</b> have been mounted to the first support rings <b>534</b> and the labels <b>538</b> have been applied to the second support rings <b>536</b>.

Example Light Emitting Apparatus

<figref idrefs="DRAWINGS">FIG. 28</figref> schematically illustrates an apparatus <b>600</b> which emits light for irradiating a patient's skin to treat portions of a patient's body underneath the patient's skin. The apparatus <b>600</b> comprises a source <b>610</b> of light having a wavelength which is substantially transmitted by the patient's skin. The apparatus <b>600</b> further comprises an optical conduit <b>620</b> optically coupled to the source <b>610</b>. The apparatus <b>600</b> further comprises an optical device <b>630</b> optically coupled to the optical conduit <b>620</b>. The optical device <b>630</b> comprises an optical diffuser <b>640</b> optically coupled to the optical conduit <b>620</b>. The optical device <b>630</b> further comprises an output optical element <b>650</b> comprising a rigid and substantially thermally conductive material. The output optical element <b>650</b> is optically coupled to the optical conduit <b>620</b> (e.g., via the optical diffuser <b>640</b>). A portion of the light transmitted through the patient's skin irradiates at least a portion of the patient's body underneath the patient's skin with an efficacious power density of light.

In certain embodiments, the source <b>610</b> comprises a laser which emits light having at least one wavelength in a range between about 630 nanometers and about 1064 nanometers. The laser of certain other embodiments emits light having at least one wavelength in a range between about 780 nanometers and about 840 nanometers. In certain embodiments, the laser emits light having a center wavelength of approximately 808 nanometers. The laser of certain embodiments is capable of generating up to approximately 6 watts of laser light and has a numerical aperture of approximately 0.16.

<figref idrefs="DRAWINGS">FIG. 29</figref> schematically illustrates an example optical conduit <b>620</b> optically coupled to an example optical device <b>630</b>. In certain embodiments, the optical conduit <b>620</b> comprises an optical fiber <b>622</b> and a protective sheath <b>624</b> around the optical fiber. The optical fiber <b>622</b> of certain embodiments is a step-index optical fiber having a numerical aperture of approximately 0.22 (e.g., a 1-millimeter diameter multimode fiber). In certain embodiments, the optical conduit <b>620</b> further comprises an electrically conductive conduit to transmit signals between the optical device <b>630</b> and the source <b>610</b> (e.g., from trigger switches or temperature sensors within the optical device <b>630</b>) and/or to provide electrical power to the optical device <b>630</b> (e.g., for a thermoelectric cooler).

In certain embodiments, the protective sheath <b>624</b> comprises a strain relief apparatus <b>625</b> and a SMA connector <b>627</b> which mechanically couples to a corresponding adjustable SMA mount <b>631</b> of the optical device <b>630</b>. The protective sheath <b>624</b> of certain embodiments has a plurality of rigid segments, with each segment having a generally cylindrical tubular shape and a longitudinal axis. Each segment is articulately coupled to neighboring segments such that an angle between the longitudinal axes of neighboring segments is limited to be less than a predetermined angle. In certain embodiments, the protective sheath <b>624</b> allows the optical conduit <b>620</b> to be moved and to bend, but advantageously limits the radius of curvature of the bend to be sufficiently large to avoid breaking the optical fiber <b>622</b> therein.

The example optical device <b>630</b> schematically illustrated by <figref idrefs="DRAWINGS">FIG. 29</figref> comprises an optical diffuser <b>640</b> and an output optical element <b>650</b> (e.g., a lens). In certain embodiments, the output optical element <b>650</b> comprises glass (e.g., BK7 glass) which is substantially optically transmissive at wavelengths which are substantially transmitted by skin, but is not substantially thermally conductive. In certain other embodiments, the output optical element <b>650</b> is rigid, substantially optically transmissive at wavelengths which are substantially transmitted by skin, and substantially thermally conductive.

In certain embodiments, the output optical element <b>650</b> has a front surface facing generally towards the patient's scalp and a back surface facing generally away from the patient's scalp. In certain embodiments, the front surface is adapted to be placed in contact with either the skin or with an intervening material in contact with the skin during irradiation. In certain such embodiments, the thermal conductivity of the output optical element <b>650</b> is sufficient to allow heat to flow from the front surface of the output optical element <b>650</b> to a heat sink in thermal communication with the back surface of the output optical element <b>650</b>. In certain embodiments, the output optical element <b>650</b> conducts heat from the front surface to the back surface at a sufficient rate to prevent, minimize, or reduce damage to the skin or discomfort to the patient from excessive heating of the skin due to the irradiation.

The existence of air gaps between the output optical element <b>650</b> and the scalp can create a problem in controlling the heating of the skin by the irradiation. In certain embodiments, the output optical element <b>650</b> is placed in contact with the skin of the scalp so as to advantageously avoid creating air gaps between the output optical element <b>650</b> and the skin. In certain other embodiments in which an intervening material is in contact with the skin and with the output optical element <b>650</b>, the output optical element <b>650</b> is placed in contact with the intervening material so as to advantageously avoid creating air gaps between the output optical element <b>650</b> and the intervening material or between the intervening material and the skin.

In certain embodiments, the thermal conductivity of the output optical element <b>650</b> has a thermal conductivity of at least approximately 10 watts/meter-K. In certain other embodiments, the thermal conductivity of the output optical element <b>650</b> is at least approximately 15 watts/meter-K. Examples of materials for the output optical element <b>650</b> in accordance with certain embodiments described herein include, but are not limited to, sapphire which has a thermal conductivity of approximately 23.1 watts/meter-K, and diamond which has a thermal conductivity between approximately 895 watts/meter-K and approximately 2300 watts/meter-K.

In certain embodiments, the optical diffuser <b>640</b> receives and diffuses light <b>626</b> emitted from the optical coupler <b>620</b> to advantageously homogenize the light beam prior to reaching the output optical element <b>650</b>. Generally, tissue optics is highly scattering, so beam non-uniformity less than approximately 3 millimeters in size has little impact on the illumination of the patient's cerebral cortex. In certain embodiments, the optical diffuser <b>640</b> advantageously homogenizes the light beam to have a non-uniformity less than approximately 3 millimeters. In certain embodiments, the optical diffuser <b>640</b> has a diffusing angle of approximately one degree.

In certain embodiments, the output optical element <b>650</b> receives the diffused light <b>626</b> propagating from the optical diffuser <b>640</b> and emits the light <b>626</b> out of the optical device <b>630</b>. In certain embodiments, the output optical element <b>650</b> comprises a collimating lens. In certain embodiments, the light beam emitted from the output optical element <b>650</b> has a nominal diameter of approximately 30 millimeters. The perimeter of the light beam used to determine the diameter of the beam is defined in certain embodiments to be those points at which the intensity of the light beam is 1/e²of the maximum intensity of the light beam. The maximum-useful diameter of certain embodiments is limited by the size of the patient's head and by the heating of the patient's head by the irradiation. The minimum-useful diameter of certain embodiments is limited by heating and by the total number of treatment sites that could be practically implemented. For example, to cover the patient's skull with a beam having a small beam diameter would correspondingly use a large number of treatment sites. In certain embodiments, the time of irradiation per treatment site can be adjusted accordingly to achieve a desired exposure dose. In certain embodiments, the beam intensity profile has a semi-Gaussian profile, while in certain other embodiments, the beam intensity profile has a “top hat” profile.

In certain embodiments, the optical device <b>630</b> comprises an optical lens which receives light from the optical conduit <b>620</b> and transmits the light to the output optical element <b>650</b>. In certain such embodiments, the output optical element <b>650</b> comprises an optical diffuser. In certain embodiments, the output optical element <b>650</b> comprises both an optical lens and an optical diffuser.

In certain embodiments, the optical device <b>630</b> further comprises a heat sink <b>660</b> thermally coupled to the output optical element <b>650</b> (e.g., by a thermal adhesive, such as Resinlab EP1200 available from Ellsworth Adhesives of Germantown, Wis.). By having the thermally conductive output optical element <b>650</b> thermally coupled to the heat sink <b>660</b>, certain embodiments advantageously provide a conduit for heat conduction away from the treatment site (e.g., the skin). In certain embodiments, the output optical element <b>650</b> is pressed against the patient's skin and transfers heat away from the treatment site. In certain other embodiments in which the output optical element <b>650</b> is pressed against an element <b>520</b> which contacts the patient's skin, as described above, the element <b>520</b> advantageously provides thermal conduction between the patient's skin and the output optical element <b>650</b>.

As schematically illustrated by <figref idrefs="DRAWINGS">FIG. 29</figref>, the heat sink <b>660</b> of certain embodiments comprises a reflective inner surface <b>662</b>, a first end <b>664</b>, and a second end <b>666</b>. The heat sink <b>660</b> is positioned so that light <b>626</b> from the optical diffuser <b>640</b> is transmitted into the first end <b>664</b>, through the heat sink <b>660</b>, out of the second end <b>666</b>, and to the output optical element <b>650</b>. The inner surface <b>662</b> of certain embodiments is substantially cylindrical, while for certain other embodiments, the inner surface <b>662</b> is substantially conical. In certain embodiments having a conical inner surface <b>662</b>, the inner surface <b>662</b> at the first end <b>664</b> has a first inner diameter and the inner surface <b>662</b> at the second end <b>666</b> has a second inner diameter larger than the first inner diameter.

In certain embodiments, the heat sink <b>660</b> comprises aluminum and the reflective inner surface is gold-plated. In certain other embodiments, the reflective inner surface <b>662</b> is roughened (e.g., by grit sandblasting) to reduce specular reflections of light from the inner surface <b>662</b>.

In certain embodiments, as schematically illustrated by <figref idrefs="DRAWINGS">FIG. 29</figref>, the optical device <b>630</b> further comprises a housing <b>670</b> comprising a plurality of ventilation slots <b>672</b>. The ventilation slots <b>672</b> of certain embodiments allow air flow to remove heat from the heat sink <b>660</b>, thereby cooling the heat sink <b>660</b>.

In certain embodiments, the housing <b>670</b> is sized to be easily held in one hand (e.g., having a length of approximately 5½ inches). The housing <b>670</b> of certain embodiments further comprises one or more protective bumpers <b>674</b> comprising a shock-dampening material (e.g., rubber). The housing <b>670</b> of certain embodiments is configured so that the optical device <b>630</b> can be held in position and sequentially moved by hand to irradiate selected portions of the patient's skin.

In certain embodiments, as schematically illustrated by <figref idrefs="DRAWINGS">FIG. 29</figref>, the optical device <b>630</b> further comprises at least one trigger switch <b>680</b>. The trigger switch <b>680</b> is electrically coupled to the source <b>610</b>. The trigger switch <b>680</b> of certain embodiments is actuated by pressing the output optical element <b>650</b> against a surface. The source <b>610</b> of certain embodiments is responsive to the trigger switch <b>680</b> by emitting light only when the trigger switch <b>680</b> is actuated. Therefore, in certain such embodiments, to utilize the optical device <b>630</b>, the output optical element <b>650</b> is pressed against the patient's skin or against an element <b>520</b>, such as described above.

In certain embodiments, the optical device <b>630</b> further comprises a thermoelectric cooler <b>690</b> thermally coupled to the output optical element <b>650</b>, as schematically illustrated by <figref idrefs="DRAWINGS">FIG. 29</figref>. The thermoelectric cooler <b>690</b> of certain embodiments has a cool side thermally coupled to the output optical element <b>650</b> and a hot side which is thermally coupled to the heat sink <b>660</b>. The thermoelectric cooler <b>690</b> of certain embodiments advantageously removes heat from the output optical element <b>650</b>. Certain embodiments of the optical device <b>630</b> comprising a thermoelectric cooler <b>690</b> which actively cools the patient's skin thereby advantageously avoiding large temperature gradients at the patient's skin which would otherwise cause discomfort to the patient. In certain embodiments, the optical device <b>630</b> further comprises one or more temperature sensors (e.g., thermocouples, thermistors) which generate electrical signals indicative of the temperature of the output optical element <b>650</b> or other portions of the optical device <b>630</b>.

<figref idrefs="DRAWINGS">FIG. 30</figref> schematically illustrates a simplified optical device <b>630</b> compatible with certain embodiments described herein. The optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 30</figref> has a smaller heat sink <b>660</b> and does not have a thermoelectric cooler. As schematically illustrated by <figref idrefs="DRAWINGS">FIG. 30</figref>, the heat sink <b>660</b> of certain embodiments comprises a reflective conical inner surface <b>662</b> having a first end <b>664</b> with a first inner diameter and a second end <b>666</b> with a second inner diameter larger than the first inner diameter. In certain embodiments, the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 30</figref> is advantageously smaller, lighter, and more easily maneuvered by hand than the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 29</figref>.

<figref idrefs="DRAWINGS">FIG. 31A</figref> illustrates two beam profile cross-sections of a light beam emitted from the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 29</figref> with the planes of the two cross-sections of <figref idrefs="DRAWINGS">FIG. 31A</figref> generally perpendicular to one another and to an output optical element <b>650</b> comprising a lens. The beam diameter of <figref idrefs="DRAWINGS">FIG. 31A</figref> is approximately 30 millimeters. <figref idrefs="DRAWINGS">FIG. 31B</figref> illustrates the encircled energy of a light beam emitted from the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 29</figref>. Approximately 90% of the encircled energy falls within a diameter of approximately 25.7 millimeters.

<figref idrefs="DRAWINGS">FIG. 32A</figref> illustrates two beam profile cross-sections of a light beam emitted from the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 30</figref> having a smooth gold-plated conical inner surface <b>662</b>. The planes of the two cross-sections of <figref idrefs="DRAWINGS">FIG. 32A</figref> are generally perpendicular to one another and to the output optical element <b>650</b>. The beam diameter of <figref idrefs="DRAWINGS">FIG. 32A</figref> is approximately 30 millimeters. The light beam has a high flux region near the center of the beam profile. This high flux region qualifies as a hot spot, where a hot spot is defined as regions of the light beam in which the local flux, averaged over a 3 millimeter by 3 millimeter area, is more than 10% larger than the average flux. <figref idrefs="DRAWINGS">FIG. 32B</figref> illustrates the encircled energy of a light beam emitted from the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 30</figref>. Approximately 90% of the encircled energy falls within a diameter of approximately 25.6 millimeters.

In certain embodiments having a smooth inner surface <b>662</b>, multiple reflections of light emitted from the optical fiber <b>622</b> at large enough angles are focused near the output optical element <b>650</b>, contributing to the hot spot region of the beam profile. <figref idrefs="DRAWINGS">FIG. 33</figref> illustrates two beam profile cross-sections of a light beam emitted from the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 30</figref> having a grit sandblasted conical inner surface <b>662</b>. This inner surface <b>662</b> is roughened to reduce the amount of specular reflections from the inner surface <b>662</b>. In certain such embodiments, the beam profile does not have a hot spot region. Certain embodiments of the optical device <b>630</b> advantageously generate a light beam substantially without hot spots, thereby avoiding large temperature gradients at the patient's skin which would otherwise cause discomfort to the patient.

In certain embodiments, the beam divergence emitted from the output optical element <b>650</b> is significantly less than the scattering angle of light inside the body tissue being irradiated, which is typically several degrees. <figref idrefs="DRAWINGS">FIGS. 34A and 34B</figref> illustrate the beam divergence for the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 29</figref> and of <figref idrefs="DRAWINGS">FIG. 30</figref> (with the sandblasted inner surface <b>622</b>), respectively. The beam divergence was measured by measuring the beam profile at two separate planes and comparing the increase in beam diameter (e.g., the diameter that encircled 90% of the energy) further from the output optical element <b>650</b>. In certain embodiments, the beam divergence has a full angle of about 12 degrees. The numerical aperture of the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 29</figref> is approximately 0.152 and the numerical aperture of the optical device <b>630</b> of <figref idrefs="DRAWINGS">FIG. 30</figref> is approximately 0.134, which equates to a difference of less than approximately 2.5 degrees.

Methods of Light Delivery

In certain embodiments, a patient is treated by identifying a plurality of treatment sites (e.g., at least about 10) on the patient's scalp, directing an electromagnetic radiation source to each of the treatment sites, and propagating electromagnetic radiation from the source to each treatment site. In certain embodiments, the electromagnetic radiation from the source has a wavelength within a range between about 800 nanometers and about 830 nanometers.

As described more fully below, in certain embodiments, the treatment sites are identified using an apparatus comprising a plurality of optically transmissive elements, each of which corresponds to a treatment site. In certain such embodiments, each of the treatment sites is irradiated by electromagnetic radiation from a source placed in contact with each of the optically transmissive elements. In certain other embodiments, the treatment sites are instead identified by other indicia. For example, each of the treatment sites can be identified by markings made on the scalp, or by structures placed in proximity to the scalp. Each of the treatment sites can then be irradiated. In certain embodiments, each of the treatment sites is irradiated by an electromagnetic radiation source in contact with the scalp or in contact with an intervening optically transmissive element which contacts the scalp. In certain other embodiments, the scalp is not contacted by either the electromagnetic radiation source or an intervening element.

In certain embodiments, each of the treatment sites is irradiated using a single electromagnetic radiation source which is sequentially moved from one treatment site to another. In certain other embodiments, a plurality of sources are used to irradiate multiple treatment sites concurrently. In certain such embodiments, the number of sources is fewer than the number of treatments sites, and the plurality of sources are sequentially moved to sequentially irradiate the treatment sites.

Methods of Use of Wearable Apparatus and Light Emitting Apparatus

<figref idrefs="DRAWINGS">FIG. 35</figref> is a flow diagram of an example method <b>700</b> for controllably exposing at least one predetermined area of a patient's scalp to laser light to irradiate the patient's brain. As described more fully below, the method <b>700</b> is described by referring to the wearable apparatus <b>500</b> and the light emitting apparatus <b>600</b> described herein. Other configurations of a wearable apparatus <b>500</b> and a light emitting apparatus <b>600</b> are also compatible with the method <b>700</b> in accordance with embodiments described herein.

The method <b>700</b> comprises providing a light emitting apparatus <b>600</b> in an operational block <b>710</b>. In certain embodiments, the light emitting apparatus <b>600</b> comprises a source <b>610</b> of laser light, an optical conduit <b>620</b> optically coupled to the source <b>610</b>, and an optical device <b>630</b> optically coupled to the optical conduit <b>620</b>. Other configurations of the light emitting apparatus <b>600</b> besides those in <figref idrefs="DRAWINGS">FIGS. 28-34</figref> are also compatible with certain embodiments described herein.

The method <b>700</b> further comprises placing a wearable apparatus <b>500</b> over the patient's scalp in an operational block <b>720</b>. The apparatus <b>500</b> comprises a body <b>510</b> and a plurality of elements <b>520</b>. Each element <b>520</b> has a first portion <b>522</b> which conforms to a corresponding portion of the patient's scalp when the apparatus <b>500</b> is worn by the patient. Each element <b>520</b> also has a second portion <b>524</b> which conforms to the optical device <b>630</b> when the optical device <b>630</b> contacts the element <b>520</b>. Each element <b>520</b> is substantially transmissive to laser light emitted by the optical device <b>630</b>. Other configurations of the wearable apparatus <b>500</b> besides those in <figref idrefs="DRAWINGS">FIGS. 19-27E</figref> are also compatible with certain embodiments described herein.

The method <b>700</b> further comprises placing the light emitting apparatus <b>600</b> in contact with an element <b>520</b> corresponding to at least a portion of the predetermined area of the patient's scalp to be irradiated in an operational block <b>730</b>. The method <b>700</b> further comprises irradiating the portion of the predetermined area of the patient's scalp with light emitted by the light emitting apparatus <b>600</b> and transmitted through the element <b>520</b> in an operational block <b>740</b>.

In certain embodiments, providing the light emitting apparatus <b>600</b> in the operational block <b>710</b> comprises preparing the light emitting apparatus <b>600</b> for use to treat the patient. In certain embodiments, preparing the light emitting apparatus <b>600</b> comprises cleaning the portion of the light emitting apparatus <b>600</b> through which laser light is outputted. In certain embodiments, preparing the light emitting apparatus <b>600</b> comprises verifying a power calibration of laser light outputted from the light emitting apparatus <b>600</b>. Such verification can comprise measuring the light intensity output from the light emitting apparatus <b>600</b> and comparing the measured intensity to an expected intensity level.

In certain embodiments, placing the wearable apparatus <b>500</b> over the patient's scalp in the operational block <b>720</b> comprises preparing the patient's scalp for treatment. For example, in certain embodiments, preparing the patient's scalp for treatment comprises removing hair from the predetermined areas of the patient's scalp to be irradiated. Removing the hair (e.g., by shaving) advantageously reduces heating of the patient's scalp by hair which absorbs laser light from the light emitting apparatus <b>600</b>. In certain embodiments, placing the wearable apparatus <b>500</b> over the patient's scalp in the operational block <b>720</b> comprises positioning the wearable apparatus <b>500</b> so that each element <b>520</b> is in contact with a corresponding portion of the patient's scalp.

In certain embodiments, placing the light emitting apparatus <b>600</b> in contact with the element <b>520</b> in the operational block <b>730</b> comprises pressing the light emitting apparatus <b>600</b> to the element <b>520</b> so that the first portion <b>522</b> of the element <b>520</b> conforms to the patient's scalp and the second portion <b>524</b> of the element <b>520</b> conforms to the light emitting apparatus <b>600</b>. In certain embodiments, by pressing the light emitting apparatus <b>600</b> against the element <b>520</b> in this way, pressure is applied to the portion of the patient's scalp in contact with the element <b>520</b> so as to advantageously blanch the portion of the patient's scalp in contact with the element <b>520</b>.

In certain embodiments, irradiating the portion of the predetermined area of the patient's scalp in the operational block <b>740</b> comprises triggering the outputting of light from the light emitting apparatus <b>600</b> by pressing the light emitting apparatus <b>600</b> against the element <b>520</b> with a predetermined level of pressure. In certain embodiments, the outputting of light from the light emitting apparatus <b>600</b> continues only if a predetermined level of pressure is maintained by pressing the light emitting apparatus <b>600</b> against the element <b>520</b>. In certain embodiments, light is outputted from the light emitting apparatus <b>600</b> through the element <b>520</b> for a predetermined period of time.

In certain embodiments, the method further comprises irradiating additional portions of the predetermined area of the patient's scalp during a treatment process. For example, after irradiating a first portion of the predetermined area corresponding to a first element <b>520</b>, as described above, the light emitting apparatus <b>600</b> can be placed in contact with a second element <b>520</b> corresponding to a second portion of the predetermined area and irradiating the second portion of the predetermined area with light emitted by the light emitting apparatus <b>600</b> and transmitted through the element <b>520</b>. The various portions of the predetermined area of the patient's scalp can be irradiated sequentially to one another in a predetermined sequence. In certain embodiments, the predetermined sequence is represented by indicia corresponding to the elements <b>520</b> of the wearable apparatus <b>500</b>. In certain such embodiments, the laser emitting apparatus <b>600</b> comprises an interlock system which interfaces with the indicia of the wearable apparatus <b>500</b> to prevent the various portions of the predetermined area from being irradiated out of the predetermined sequence.

In certain embodiments, a system for treating a patient comprises a support (e.g., a wearable apparatus <b>500</b> as described herein) for identifying a plurality of sites on a patient's scalp for the application of therapeutic electromagnetic energy in a wavelength range between about 800 nanometers and about 830 nanometers. The system further comprises an instruction for use of the support in combination with an electromagnetic light source (e.g., a light emitting apparatus <b>600</b> as described herein) of the therapeutic electromagnetic energy. The instruction for use in certain embodiments comprises instructions compatible with the method <b>700</b> described herein.

In certain embodiments, a system for treating a patient comprises an electromagnetic light source (e.g., a light emitting apparatus <b>600</b> as described herein). The system further comprises an instruction for use of the electromagnetic radiation source by optically coupling the source to a patient's scalp at a plurality of locations to deliver a therapeutic electromagnetic energy to the patient's brain. The instruction for use in certain embodiments comprises instructions compatible with the method <b>700</b> described herein.

Methods of Phototherapy

Certain embodiments utilizing phototherapy as described herein are based at least in part on the finding described above that, for a selected wavelength, the power density (light intensity or power per unit area, in W/cm²) or the energy density (energy per unit area, in J/cm², or power density multiplied by the exposure time) of the light energy delivered to tissue is an important factor in determining the relative efficacy of the phototherapy, and efficacy is not as directly related to the total power or the total energy delivered to the tissue. In the methods described herein, power density or energy density as delivered to a portion of the patient's brain <b>20</b>, which can include an area affected by neurodegenerative disease (e.g., Parkinson's disease), appears to be important factors in using phototherapy to treat the brain <b>20</b>. Certain embodiments apply optimal power densities or energy densities to the intended target tissue, within acceptable margins of error.

As described in U.S. Patent Application Publication Nos. 2004/0138727A1, 2007/0179570A1, and 2007/0179571A1, each of which is incorporated in its entirety by reference herein, this discovery has been is particularly applicable with respect to treating and saving surviving but endangered neurons after stroke (e.g., in a zone of danger surrounding the primary infarct after a stroke or cerebrovascular accident). Without being bound by theory or by a specific mechanism, it is believed that light energy delivered within a certain range of power densities and energy densities provides the desired biostimulative effect on the intracellular environment, such that proper function is returned to previously nonfunctioning or poorly functioning mitochondria in neurons which are at risk due to stroke. The biostimulative effect may include interactions with chromophores within the target tissue, which facilitate production of ATP thereby feeding energy to injured cells which have experienced decreased blood flow due to the stroke. Because strokes correspond to blockages or other interruptions of blood flow to portions of the brain, it is thought that any effects of increasing blood flow by phototherapy are of less importance in the efficacy of phototherapy for stroke victims. Further information regarding the role of power density and exposure time is described by Hans H. F. I. van Breugel and P. R. Dop Bar in “Power Density and Exposure Time of He—Ne Laser Irradiation Are More Important Than Total Energy Dose in Photo-Biomodulation of Human Fibroblasts In Vitro,” Lasers in Surgery and Medicine, Volume 12, pp. 528-537 (1992), which is incorporated in its entirety by reference herein.

A prominent feature of early Parkinson's disease is the damage to the neuronal processes (axons and their synapses) that communicate with other neurons. Axons are thin, cylindrical processes that extend so far from the neuronal cell that they require an axonal transport system to supply vital nutrients and important organelles like mitochondria and synaptic vesicles. One recent hypothesis to explain why axons and synapses are damaged in Parkinson's disease patients is a failure in the axonal transport system in dopaminergic neurons.

To determine if axonal transport is defective, two different models of sporadic Parkinson's disease have been previously used in studies by Dr. Patricia Trimmer et al. of the University of Virginia Department of Neuroscience. In these studies, axonal transport of mitochondria was found to be significantly reduced in processes of Parkinson's disease cybrids (unique human neuronal cell lines that contain the mitochondrial DNA of individual Parkinson's disease patients and which share many important attributes with injured dopaminergic neurons in the brains of Parkinson's disease patients) and similar human neuronal cells exposed to rotenone (a pesticide that damages neurons in a manner that resembles Parkinson's disease). These findings strongly support the hypothesis that reduced axonal transport plays an important role in the early stages of Parkinson's disease.

Studies which have exposed Parkinson's disease cybrid cells and rotenone-treated neuronal cells to low energy laser treatment have found that axonal transport of mitochondria was restored. Such studies illustrate that low energy laser treatment can improve the supply of vital nutrients and organelles to axons and synapses in Parkinson's disease to compensate at least in part for the reduced axonal transport. In view of the hypothesis that axonal transport of essential nutrients is reduced in Parkinson's disease, certain embodiments described herein advantageously provide low energy laser treatment to combat this reduction of transport. In certain embodiments described herein, delivering electromagnetic radiation to brain cells causes an improvement of mitochondrial function in irradiated neurons.

In certain embodiments, the apparatus and methods of phototherapy described herein increase the cerebral blood flow of the patient. In certain such embodiments, the cerebral blood flow is increased by 10%, 15%, 20%, or 25% immediately post-irradiation, as compared to immediately prior to irradiation.

In certain embodiments, the apparatus and methods of phototherapy described herein are used to treat neurodegeneration. As used herein, the term “neurodegeneration” refers to the process of cell destruction resulting from primary destructive events such as stroke or cerebrovascular accident, as well as from secondary, delayed and progressive destructive mechanisms that are invoked by cells due to the occurrence of the primary destructive event. Primary destructive events include disease processes or physical injury or insult, including stroke, but also include other diseases and conditions such as multiple sclerosis, amylotrophic lateral sclerosis, heat stroke, epilepsy, Alzheimer's disease, dementia resulting from other causes such as AIDS, cerebral ischemia including focal cerebral ischemia, and physical trauma such as crush or compression injury in the CNS, including a crush or compression injury of the brain, spinal cord, nerves or retina, or any acute injury or insult producing neurodegeneration. Secondary destructive mechanisms include any mechanism that leads to the generation and release of neurotoxic molecules, including apoptosis, depletion of cellular energy stores because of changes in mitochondrial membrane permeability, release or failure in the reuptake of excessive glutamate, reperfusion injury, and activity of cytokines and inflammation. Both primary and secondary mechanisms contribute to forming a “zone of danger” for neurons, wherein the neurons in the zone have at least temporarily survived the primary destructive event, but are at risk of dying due to processes having delayed effect.

As used herein, the term “neuroprotection” refers to a therapeutic strategy for slowing or preventing the otherwise irreversible loss of neurons due to neurodegeneration after a primary destructive event, whether the neurodegeneration loss is due to disease mechanisms associated with the primary destructive event or secondary destructive mechanisms.

The term “cognitive function” as used herein refers to cognition and cognitive or mental processes or functions, including those relating to knowing, thinking, learning, perception, memory (including immediate, recent, or remote memory), and judging. Symptoms of loss of cognitive function can also include changes in personality, mood, and behavior of the patient. Diseases or conditions affecting cognitive function include Alzheimer's disease, dementia, AIDS or HIV infection, Cruetzfeldt-Jakob disease, head trauma (including single-event trauma and long-term trauma such as multiple concussions or other traumas which may result from athletic injury), Lewy body disease, Pick's disease, Parkinson's disease, Huntington's disease, drug or alcohol abuse, brain tumors, hydrocephalus, kidney or liver disease, stroke, depression, and other mental diseases which cause disruption in cognitive function, and neurodegeneration.

The term “motor function” as used herein refers to those bodily functions relating to muscular movements, primarily conscious muscular movements, including motor coordination, performance of simple and complex motor acts, and the like.

The term “neurologic function” as used herein includes both cognitive function and motor function.

The terms “cognitive enhancement” and “motor enhancement” as used herein refer to the improving or heightening of cognitive function and motor function, respectively.

The term “neurologic enhancement” as used herein includes both cognitive enhancement and motor enhancement.

As used herein, the term “neuroprotective-effective” as used herein refers to a characteristic of an amount of light energy, wherein the amount is a power density of the light energy measured in mW/cm². A neuroprotective-effective amount of light energy achieves the goal of preventing, avoiding, reducing, or eliminating neurodegeneration, which should result in cognitive enhancement and/or motor enhancement.

The term “neurologic function enhancement effective” as used herein refers to a characteristic of an amount of light energy, wherein the amount is a power density of the light energy measured in mW/cm². The amount of light energy achieves the goal of neuroprotection, motor enhancement, and/or cognitive enhancement.

Thus, a method for the treatment or enhancement of neurologic function in a patient in need of such treatment involves delivering a neurologic function enhancement effective amount or a neuroprotective-effective amount of light energy having a wavelength in the visible to near-infrared wavelength range to a target area of the patient's brain <b>20</b>. In certain embodiments, the target area of the patient's brain <b>20</b> includes an area exhibiting neurodegeneration. In other embodiments, the target area includes portions of the brain <b>20</b> not exhibiting neurodegeneration. Without being bound by theory or by a specific mechanism, it is believed that irradiation of healthy tissue in proximity to the area exhibiting neurodegeneration increases the production of ATP and copper ions in the healthy tissue and which then migrate to cells exhibiting neurodegeneration, thereby producing beneficial effects. Additional information regarding the biomedical mechanisms or reactions involved in phototherapy is provided by Tiina I. Karu in “Mechanisms of Low-Power Laser Light Action on Cellular Level”, Proceedings of SPIE Vol. 4159 (2000), Effects of Low-Power Light on Biological Systems V, Ed. Rachel Lubart, pp. 1-17, which is incorporated in its entirety by reference herein.

In certain embodiments, delivering the neuroprotective amount of light energy includes selecting a surface power density of the light energy at the scalp <b>30</b> corresponding to the predetermined power density at the target area of the brain <b>20</b>. As described above, light propagating through tissue is scattered and absorbed by the tissue. Calculations of the power density to be applied to the scalp <b>30</b> so as to deliver a predetermined power density to the selected target area of the brain <b>20</b> preferably take into account the attenuation of the light energy as it propagates through the skin and other tissues, such as bone and brain tissue. Factors known to affect the attenuation of light propagating to the brain <b>20</b> from the scalp <b>30</b> include, but are not limited to, skin pigmentation, the presence and color of hair over the area to be treated, amount of fat tissue, the presence of bruised tissue, skull thickness, and the location of the target area of the brain <b>20</b>, particularly the depth of the area relative to the surface of the scalp <b>30</b>. For example, to obtain a desired power density of 50 mW/cm²in the brain <b>20</b> at a depth of 3 cm below the surface of the scalp <b>30</b>, phototherapy may utilize an applied power density of 500 mW/cm². The higher the level of skin pigmentation, the higher the power density applied to the scalp <b>30</b> to deliver a predetermined power density of light energy to a subsurface site of the brain <b>20</b>.

In certain embodiments, treating a patient suffering from the effects of neurodegenerative disease (e.g., Parkinson's disease) comprises placing the therapy apparatus <b>10</b> in contact with the scalp <b>30</b> and adjacent the target area of the patient's brain <b>20</b>. The target area of the patient's brain <b>20</b> can be previously identified such as by using standard medical imaging techniques. In certain embodiments, treatment further includes calculating a surface power density at the scalp <b>30</b> which corresponds to a preselected power density at the target area of the patient's brain <b>20</b>. The calculation of certain embodiments includes factors that affect the penetration of the light energy and thus the power density at the target area. These factors include, but are not limited to, the thickness of the patient's skull, type of hair and hair coloration, skin coloration and pigmentation, patient's age, patient's gender, and the distance to the target area within the brain <b>20</b>. The power density and other parameters of the applied light are then adjusted according to the results of the calculation.

The power density selected to be applied to the target area of the patient's brain <b>20</b> depends on a number of factors, including, but not limited to, the wavelength of the applied light, the type of CVA (ischemic or hemorrhagic), and the patient's clinical condition, including the extent of the affected brain area. The power density of light energy to be delivered to the target area of the patient's brain <b>20</b> may also be adjusted to be combined with any other therapeutic agent or agents, especially pharmaceutical neuroprotective agents, to achieve the desired biological effect. In such embodiments, the selected power density can also depend on the additional therapeutic agent or agents chosen.

In certain embodiments, the treatment per treatment site proceeds continuously for a period of about 10 seconds to about 2 hours, more preferably for a period of about 1 to about 10 minutes, and most preferably for a period of about 1 to 5 minutes. For example, the treatment time per treatment site in certain embodiments is about two minutes. In other embodiments, the light energy is preferably delivered for at least one treatment period of at least about five minutes, and more preferably for at least one treatment period of at least ten minutes. The minimum treatment time of certain embodiments is limited by the biological response time (which is on the order of microseconds). The maximum treatment time of certain embodiments is limited by heating and by practical treatment times. The light energy can be pulsed during the treatment period or the light energy can be continuously applied during the treatment period.

In certain embodiments, the treatment may be terminated after one treatment period, while in other embodiments, the treatment may be repeated for at least two treatment periods. The time between subsequent treatment periods is preferably at least about five minutes, more preferably at least about 1 to 2 days, and most preferably at least about one week. In certain embodiments in which treatment is performed over the course of multiple days, the apparatus <b>10</b> is wearable over multiple concurrent days (e.g., embodiments of <figref idrefs="DRAWINGS">FIGS. 1</figref>, <b>3</b>, <b>9</b>A, <b>10</b>, and <b>13</b>). The length of treatment time and frequency of treatment periods can depend on several factors, including the functional recovery of the patient and the results of imaging analysis of the infarct. In certain embodiments, one or more treatment parameters can be adjusted in response to a feedback signal from a device (e.g., magnetic resonance imaging) monitoring the patient.

During the treatment, the light energy may be continuously provided, or it may be pulsed. If the light is pulsed, the pulses are preferably at least about 10 nanosecond long and occur at a frequency of up to about 100 kHz. In certain embodiments in which the target brain tissue to be irradiated is deeper within the brain (e.g., 4 centimeters or more below the dura), pulsing can be used to achieve the desired power densities at the target brain tissue while reducing the heat load and the corresponding temperature increases. For example, pulsing may be used to irradiate the substantia nigra of the patient's brain. In certain other embodiments, continuous wave light may also be used.

In certain embodiments, the phototherapy is combined with other types of treatments for an improved therapeutic effect. Treatment can comprise directing light through the scalp of the patient to a target area of the brain concurrently with applying an electromagnetic field to the brain. In such embodiments, the light has an efficacious power density at the target area and the electromagnetic field has an efficacious field strength. For example, the apparatus <b>50</b> can also include systems for electromagnetic treatment, e.g., as described in U.S. Pat. No. 6,042,531 issued to Holcomb, which is incorporated in its entirety by reference herein. In certain embodiments, the electromagnetic field comprises a magnetic field, while in other embodiments, the electromagnetic field comprises a radio-frequency (RF) field. As another example, treatment can comprise directing an efficacious power density of light through the scalp of the patient to a target area of the brain concurrently with applying an efficacious amount of ultrasonic energy to the brain. Such a system can include systems for ultrasonic treatment, e.g., as described in U.S. Pat. No. 5,054,470 issued to Fry et al., which is incorporated in its entirety by reference herein.

PHOTOTHERAPY EXAMPLES

Example 1

An in vitro experiment was done to demonstrate one effect of phototherapy on neurons, namely the effect on ATP production. Normal Human Neural Progenitor (NHNP) cells were obtained cryopreserved through Clonetics of Baltimore, Md., catalog #CC-2599. The NHNP cells were thawed and cultured on polyethyleneimine (PEI) with reagents provided with the cells, following the manufacturers' instructions. The cells were plated into 96 well plates (black plastic with clear bottoms, Becton Dickinson of Franklin Lakes, N.J.) as spheroids and allowed to differentiate into mature neurons over a period of two weeks.

A Photo Dosing Assembly (PDA) was used to provide precisely metered doses of laser light to the NHNP cells in the 96 well plates. The PDA included a Nikon Diaphot inverted microscope (Nikon of Melville, N.Y.) with a LUDL motorized x, y, z stage (Ludl Electronic Products of Hawthorne, N.Y.). An 808 nanometer laser was routed into the rear epi-fluorescent port on the microscope using a custom designed adapter and a fiber optic cable. Diffusing lenses were mounted in the path of the beam to create a “speckled” pattern, which was intended to mimic in vivo conditions after a laser beam passed through human skin. The beam diverged to a 25 millimeter diameter circle when it reached the bottom of the 96 well plates. This dimension was chosen so that a cluster of four adjacent wells could be lased at the same time. Cells were plated in a pattern such that a total of 12 clusters could be lased per 96 well plate. Stage positioning was controlled by a Silicon Graphics workstation and laser timing was performed by hand using a digital timer. The measured power density passing through the plate for the NHNP cells was 50 mW/cm².

Two independent assays were used to measure the effects of 808 nanometer laser light on the NHNP cells. The first was the CellTiter-Glo Luminescent Cell Viability Assay (Promega of Madison, Wis.). This assay generates a “glow-type” luminescent signal produced by a luciferase reaction with cellular ATP. The CellTiter-Glo reagent is added in an amount equal to the volume of media in the well and results in cell lysis followed by a sustained luminescent reaction that was measured using a Reporter luminometer (Turner Biosystems of Sunnyvale, Calif.). Amounts of ATP present in the NHNP cells were quantified in Relative Luminescent Units (RLUs) by the luminometer.

The second assay used was the alamarBlue assay (Biosource of Camarillo, Calif.). The internal environment of a proliferating cell is more reduced than that of a non-proliferating cell. Specifically, the ratios of NADPH/NADP, FADH/FAD, FMNH/FMN and NADH/NAD, increase during proliferation. Laser irradiation is also thought to have an effect on these ratios. Compounds such as alamarBlue are reduced by these metabolic intermediates and can be used to monitor cellular states. The oxidization of alamarBlue is accompanied by a measurable shift in color. In its unoxidized state, alamarBlue appears blue; when oxidized, the color changes to red. To quantify this shift, a 340PC microplate reading spectrophotometer (Molecular Devices of Sunnyvale, Calif.) was used to measure the absorbance of a well containing NHNP cells, media and alamarBlue diluted 10% v/v. The absorbance of each well was measured at 570 nanometers and 600 nanometers and the percent reduction of alamarBlue was calculated using an equation provided by the manufacturer.

The two metrics described above, (RLUs and % Reduction) were then used to compare NHNP culture wells that had been lased with 50 mW/cm²at a wavelength of 808 nanometers. For the CellTiter-Glo assay, 20 wells were lased for 1 second and compared to an unlased control group of 20 wells. The CellTiter-Glo reagent was added 10 minutes after lasing completed and the plate was read after the cells had lysed and the luciferase reaction had stabilized. The average RLUs measured for the control wells was 3808+/−3394 while the laser group showed a two-fold increase in ATP content to 7513+/−6109. The standard deviations were somewhat high due to the relatively small number of NHNP cells in the wells (approximately 100 per well from visual observation), but a student's unpaired t-test was performed on the data with a resulting p-value of 0.02 indicating that the two-fold change is statistically significant.

The alamarBlue assay was performed with a higher cell density and a lasing time of 5 seconds. The plating density (calculated to be between 7,500-26,000 cells per well based on the certificate of analysis provided by the manufacturer) was difficult to determine since some of the cells had remained in the spheroids and had not completely differentiated. Wells from the same plate can still be compared though, since plating conditions were identical. The alamarBlue was added immediately after lasing and the absorbance was measured 9.5 hours later. The average measured values for percent reduction were 22%+/−7.3% for the 8 lased wells and 12.4%+/−5.9% for the 3 unlased control wells (p-value=0.076). These alamarBlue results support the earlier findings in that they show a similar positive effect of the laser treatment on the cells.

Increases in cellular ATP concentration and a more reduced state within the cell are both related to cellular metabolism and are considered to be indications that the cell is viable and healthy. These results are novel and significant in that they show the positive effects of laser irradiation on cellular metabolism in in-vitro neuronal cell cultures.

Example 2

In a second example, transcranial laser therapy for stroke was investigated using a low-energy infrared laser to treat behavioral deficits in a rabbit small clot embolic stroke model (RSCEM). This example is described in more detail by P. A. Lapchak et al., “<i>Transcranial Infrared Laser Therapy Improves Clinical Rating Scores After Embolic Strokes in Rabbits,” Stroke</i>, Vol. 35, pp. 1985-1988 (2004), which is incorporated in its entirety by reference herein.

RSCEM was produced by injection of blood clots into the cerebral vasculature of anesthetized male New Zealand White rabbits, resulting in ischemia-induced behavioral deficits that can be measured quantitatively with a dichotomous rating scale. In the absence of treatment, small numbers of microclots caused no grossly apparent neurologic dysfunction while large numbers of microclots invariably caused encephalopathy or death. Behaviorally normal rabbits did not have any signs of impairment, whereas behaviorally abnormal rabbits had loss of balance, head leans, circling, seizure-type activity, or limb paralysis.

For laser treatment, a laser probe was placed in direct contact with the skin. The laser probe comprised a low-energy laser (wavelength of 808±5 nanometers) fitted with an OZ Optics Ltd. fiber-optic cable and a laser probe with a diameter of approximately 2 centimeters. Instrument design studies showed that these specifications would allow for laser penetration of the rabbit skull and brain to a depth of 2.5 to 3 centimeters, and that the laser beam would encompass the majority of the brain if placed on the skin surface posterior to bregma on the midline. Although the surface skin temperature below the probe was elevated by up to 3° C., the focal brain temperature directly under the laser probe was increased by 0.8° C. to 1.8° C. during the 10-minute laser treatment using the 25 mW/cm²energy setting. Focal brain temperature returned to normal within 60 minutes of laser treatment.

The quantitative relationship between clot dose and behavioral or neurological deficits was evaluated using logistic (S-shaped) curves fitted by computer to the quantal dose-response data. These parameters are measures of the amount of microclots (in mg) that produced neurologic dysfunction in 50% of a group of animals (P₅₀). A separate curve was generated for each treatment condition, with a statistically significant increase in the P₅₀value compared with control being indicative of a behavioral improvement. The data were analyzed using the t test, which included the Bonferroni correction when appropriate.

To determine if laser treatment altered physiological variables, 14 rabbits were randomly divided into 2 groups, a control group and a laser-treated group (25 mW/cm²for 10 minutes). Blood glucose levels were measured for all embolized rabbits using a Bayer Elite XL 3901 B Glucometer, and body temperature was measured using a Braun Thermoscan Type 6013 digital thermometer. Within 60 minutes of embolization, there was an increase in blood glucose levels in both the control group and the laser-treated group that was maintained for the 2 hours post-embolization observation time. Blood glucose levels returned to control levels by 24 hours, regardless of the extent of stroke-induced behavioral deficits. Laser treatment did not significantly affect glucose levels at any time. Neither embolization nor laser treatment significantly affected body temperature in either group of rabbits.

<figref idrefs="DRAWINGS">FIG. 17A</figref> is a graph for the percentage of the population which was either abnormal or dead as a function of the clot weight in milligrams for laser treatment of 7.5 mW/cm²for a treatment duration of 2 minutes. As shown by <figref idrefs="DRAWINGS">FIG. 17A</figref>, the control curve (dotted line) has a P₅₀value of 0.97±0.19 mg (n=23). Such laser treatment initiated 3 hours after the stroke significantly improved behavioral performance, with the P₅₀value increased to 2.21±0.54 mg (n=28, *P=0/05) (solid line). The effect was durable and was measurable 3 weeks after embolization. However, the same setting did not improve behavior if there was a long delay (24 hours) after embolization (dashed line) (P₅₀=1.23±0.15 mg, n=32).

<figref idrefs="DRAWINGS">FIG. 17B</figref> is a graph for the percentage of the population which was either abnormal or dead as a function of the clot weight in milligrams for laser treatment of 25 mW/cm2 for a treatment duration of 10 minutes. As shown by <figref idrefs="DRAWINGS">FIG. 17B</figref>, the control curve (dotted line) has a P₅₀value of 1.10±0.17 mg (n=27). Such laser treatment initiated 1 (dashed line) or 6 (solid line) hours after embolization also significantly increased behavioral performance, with the P₅₀value increased to 2.02±0.46 mg (n=18, *P&lt;0.05) and 2.98±0.65 mg (n=26, *P&lt;0.05), respectively.

<figref idrefs="DRAWINGS">FIG. 18</figref> is a graph showing the therapeutic window for laser-induced behavioral improvements after small-clot embolic strokes in rabbits. Results are shown as clinical rating score P₅₀(mg clot) given as mean±SEM for the number of rabbits per time point (number in brackets) for laser treatment initiated 1, 3, 6, or 24 hours after embolization as shown on the x-axis. The horizontal line represents the mean of the control P₅₀values (*P&lt;0.05).

The results in the RSCEM showed that laser treatment significantly improved behavioral rating scores after embolic strokes in rabbits without affecting body temperature and blood glucose levels. In addition, laser treatment was effective when initiated up to 6 hours after strokes, which is later than any other previously effective single therapy in the same preclinical stroke model. Moreover, the effect was durable and was measurable up to 21 days after embolization. The magnitudes of laser-induced improvement in rabbits are similar to previously tested thrombolytics (alteplase, tenecteplase, and microplasmin) and neuroprotective compounds (NXY-059), which are undergoing clinical development.

Neurologic Function Scales

Neurologic function scales can be used to quantify or otherwise characterize the efficacy of various embodiments described herein. Neurologic function scales generally use a number of levels or points, each point corresponding to an aspect of the patient's condition. The number of points for a patient can be used to quantify the patient's condition, and improvements in the patient's condition can be expressed by changes of the number of points. One example neurologic function scale used as a clinical tool for diagnosis and determining severity of Parkinson's disease is the Unified Parkinson's Disease Rating Scale (UPDRS) which comprises various sections evaluated by interview and clinical observation. In certain embodiments, two or more of the neurologic function scales can be used in combination with one another, and can provide longer-term measurements of efficacy (e.g., at three months).

In certain embodiments described herein, a patient exhibiting symptoms of Parkinson's disease is treated by irradiating a plurality of treatment sites on the patient's scalp. The irradiation is performed utilizing irradiation parameters (e.g., wavelength, power density, time period of irradiation, etc.) which, when applied to members of a treated group of patients, produce at least a 2% average difference between the treated group and a placebo group on at least one neurologic function scale (e.g., UPDRS) analyzed in dichotomized or any other fashion. Certain other embodiments produce at least a 4% average difference, at least a 6% average difference, or at least a 10% average difference between treated and placebo groups on at least one neurologic function scale analyzed in dichotomized or any other fashion. In certain embodiments, the irradiation of the patient's scalp produces a change in the patient's condition. In certain such embodiments, the change in the patient's condition corresponds to a change in the number of points indicative of the patient's condition. In certain such embodiments, the irradiation produces a change of one point, a change of two points, a change of three points, or a change of more than three points on a neurologic function scale.

Possible Action Mechanisms

The following section discusses theories and potential action mechanisms, as they presently appear to the inventors, for certain embodiments of phototherapy described herein. The scope of the claims of the present application is not to be construed to depend on the accuracy, relevance, or specifics of any of these theories or potential action mechanisms. Thus the claims of the present application are to be construed without being bound by theory or by a specific mechanism.

It is well known that light can produce profound biological effects such as vision, regulation of circadian hormones, melanin production, and Vitamin D synthesis. It has also been shown that specific wavelengths of light targeted at the cytochrome C receptor in the mitochondria can dramatically preserve function, as well as, reduce the size of myocardial infarcts and stroke. It has also been shown that these effects can be reproduced across multiple species. This is not surprising since the mitochondrial target receptor (i.e., copper ions in cytochrome C) is conserved between species. These effects may be due to production of new cells (neurogenesis), preservation of existing tissue (neuroprotection) or a combination of both.

The clinical and cellular responses to light for in vivo treatment efficacy of ischemic conditions of acute myocardial infarction and stroke has been demonstrated in multiple validated animal models. As described more fully below, these effects are wavelength-specific. Without being bound by theory or by a specific mechanism, the wavelength specificity may be dependent upon a known mitochondrial receptor (cyctochrome C oxidase). Targeting of this receptor may result in formation of adenosine triphosphate (ATP), enhanced mitochondrial survival, and maintenance of cytochrome C oxidase activity.

In stroke, the occlusion of a major artery results in a core area of severe ischemia (e.g., with blood flow reduced to less than 20% of pre-occlusion levels). The core area has a rapid loss of ATP and energy production, and the neurons are depolarized. This core of the infarct is surrounded by an ischemic penumbra which can be up to twice as large as the core of the infarct. Cells within the penumbra show less severe decreases in loss of blood flow (e.g., 20 to 40% of normal). Neurons in the penumbra tend to be hyperpolarized and electrically silent. In the penumbra, the cells undergo progression of cell death lasting from hours to days after the infarct. Also, inflammation after infarct can play a role in determining the final infarct size and anti-inflammatory modulators can reduce infarct size. The infarct is dynamic, with different parts of the infarct being affected to different degrees over a period of hours to days. Photon therapy has been implicated in a number of physiological processes that could favor cell survival in the penumbral region of a stroke.

In Vitro

The action of light on a cell is mediated by one or more specific photo acceptors. A photo acceptor molecule first absorbs the light. After this absorptive event and promotion of an electron to an excited state, one or more primary molecular processes from these high energy states can lead to a measurable biological effect at the cellular level. An action spectra represents the biological activity as a function of wavelength, frequency or photon energy. Karu was the first researcher to propose that the action spectra should resemble the absorption spectra of the photoacceptor molecule. Since an absorptive event occurs for a transfer of energy to take place, the stimulatory wavelengths of the action spectra falls within the absorptive spectra of the photo acceptor.

Karu was also the first to propose a specific mechanism for photon therapy at the cellular level (see, e.g., T. Karu, “<i>Photobiological Fundamentals of Low Power Laser Therapy,” IEEE Journal of Quantum Electronics, </i>1987, Vol. 23, page 1703; T. Karu, “<i>Mechanisms of interaction of monochromatic visible light with cells,” Proc. SPIE, </i>1995, Vol. 2630, pages 2-9). Karu's hypothesis was based on the absorption of monochromatic visible and near infrared radiation by components of the cellular respiratory chain. Absorption and promotion of electronically excited states cause changes in redox properties of these molecules and acceleration of electron transfer (primary reactions). Primary reactions in mitochondria of eukaryotic cells are followed by a cascade of secondary reactions occurring in the cytoplasm, cell membrane, and nucleus. Karu defined the action spectra for mammalian cells of several secondary reactions (DNA, RNA synthesis, cellular adhesion). The action spectra for all of these secondary markers were very similar, suggesting a common photo acceptor. Karu then compared these action spectra with absorption spectra of the copper centers of cytochrome C oxidase in both reduced and oxidized states. Cytochrome C oxidase contains four redox active metal centers and has a strong absorbance in the near infrared spectral range. The spectral absorbance of cytochrome C oxidase and the action spectra were very similar. Based on this, Karu suggested that the primary photoacceptors are mixed valence copper centers within cytochrome C oxidase.

Cytochrome C oxidase is the terminal enzyme of the mitochondrial electron transport chain of all eukaryotes and is required for the proper function of almost all cells, especially those of highly metabolically active organs, such as the brain and heart. Cytochrome C has also been suggested to be the critical chromophore responsible for stimulatory effects of irradiation with infrared light to reverse the reduction in cytochrome C oxidase activity produced by the blockade of voltage dependent sodium channels with tetrodotoxin and up regulated cytochrome C activity in primary neuronal cells. It has been demonstrated by researchers (see, e.g., M. T. Wong-Riley et al., <i>NeuroReport, </i>2001, Vol. 12, pages 3033-3037; J. T. Eells et al., <i>Proceedings National Academy of Science, </i>2003, Vol. 100, pages 3439-3444) that in vivo, rat retinal neurons are protected from damage induced by methanol intoxication. Methanol's toxic metabolite is formic acid which inhibits cytochrome C.

Several investigators have demonstrated the increased synthesis of ATP from infrared irradiation both in vitro and in vivo. Karu has shown that irradiation of cells in vitro at wavelengths of 632 nanometers, 670 nanometers, and 820 nanometers can increase mitochondrial activity.

In Vivo

There are numerous studies, both published and unpublished, demonstrating the effectiveness of photon therapy in animal models for acute myocardial infarction (AMI) and ischemic stroke. These studies suggest that photon therapy induces a cascade of signaling events initiated by the initial absorption of light by cytochrome C. These signaling events apparently up-and-down regulate genes, transcription factors, as well as increase mitochondrial function.

Without being bound by theory or a specific mechanism, in stroke, reduction of infarct volume may occur in one of two ways or a combination of both: (i) preservation of existing tissue (neuroprotection), and (ii) generation of new tissue (neurogenesis). A number in vitro and in vivo studies appear to support both of these potential mechanisms. The potential effects of NIR light on neurogenesis are straightforward; it either increases the number of new cells, or it prevents the loss of new cells that are generated as a result of the ischemic insult. Neuroprotection can result from at least three mechanisms: (i) direct stimulation of tissue survival; (ii) indirect stimulation of tissue survival (e.g., increased growth factor activity); and (iii) decrease in toxic factors.

<figref idrefs="DRAWINGS">FIG. 36</figref> is a graph which shows mediators responsible for ischemic stroke tissue damage and the time points at which they occur. <figref idrefs="DRAWINGS">FIG. 36</figref> illustrates several potential places where photon therapy could potentially intervene to reduce infarct severity. Early after ischemic stroke, excitatory amino acids (EAAs) induce Ca²⁺ influx via NMDA receptor activation leading to neuronal and glial cell injury. A number of immediately early genes (IEGs) express such as c-fos, c-jun, within 30 minutes. Reactive oxygen species (ROSs) create lipid peroxidation and activated phagocytes which create further injury. ROSs damage most cellular components. Cytokines are then expressed causing migration of polymorphonuclear neutrophils (PMNs) into the ischemic brain. Macrophages and neutrophils follow into the brain parenchyma. Apoptosis occurs via caspase activation which further increases stroke damage.

Preservation of existing tissue (neuroprotection) can result from direct stimulation of the tissue (e.g., by ATP synthesis or by prevention of cytochrome C release from mitochondria). Ischemia results in depletion of ATP in the ischemic zone due to lack of oxygen and glucose. The resultant lack of ATP, depending on severity, results in decreased cellular function. In extreme cases, energy depletion leads to cell depolarization, calcium influx, and activation of necrotic and apoptotic processes. Near-infrared radiation (NIR) stimulates the production of ATP in a variety of cell types in culture, and in cardiac tissue. A single irradiation of infarcted cardiac tissue results in a statistically significant 3-fold increase in tissue ATP levels four hours after treatment. The effect of NIR is prolonged long after irradiation is ceased. The prolonged effect could also be due, in part, to preservation of mitochondrial function. NIR irradiated, infarcted cardiac tissue has exhibited over a 50% reduction in damaged mitochondria. After ischemia, the myocardial tissue that is not immediately lost is in a “stunned” state, and can remain stunned for a period of days. In particular, it is the mitochondria in the tissue that are stunned. Stunned mitochondria are still intact, but with characteristic morphological changes that are indicative of mitochondria that are not metabolically active. As such, even with restored blood flow, the mitochondria are unable to convert oxygen and glucose to useable energy (ATP).

Neuroprotection can also result from direct stimulation of the tissue by preventing cytochrome C release from mitochondria. The release of cytochrome C from the mitochondria into the cytoplasm is a potent apoptotic signal. Cytochrome C release results in the activation of caspase-3 and activation of apoptotic pathways. The apoptotic cells appear as soon as a few hours after stroke, but the cell numbers peak at 24 to 48 hours after reperfusion. In rat models of stroke, cytoplasmic cytochrome C can be detected out to at least 24 hours after the occlusion. In vitro 810-nanometer light can prevent the TTX-induced decrease in cytochrome oxidase activity. Photon therapy may also be able to maintain cytochrome oxidase activity in vivo by preventing release of cytochrome C into the cytoplasm, resulting in the prevention of apoptosis. The release of cytochrome C is regulated by the Bcl/Bax system. Bax promotes release and Bcl decreases release. In myofiber cultures in vitro, NIR light promotes Bcl-2 expression and inhibits Bax expression, which fits with the prevention of cytochrome C release data.

Neuroprotection can also result from indirect stimulation (e.g., by angiogenesis or by up-regulation of cell survival genes and/or growth factors). Regarding angiogenesis and stroke, recent research indicates that the reduction in cerebral blood flow (CBF) can lead to compensatory neovascularization in the affected regions. The low CBF results in the up regulation of hypoxia inducible factor-1 (HIF-1), vascular endothelial growth factor (VEGF), and VEGF receptors. In the rat pMCAo model, infusion of VEGF results in a reduction of infarct size. In AMI models, VEGF is increased with photon therapy.

Regarding up-regulation of cell survival genes and/or growth factors, it has been shown that photon therapy may up-, and down-regulate certain beneficial genes. It is possible that these gene products can prevent or ameliorate apoptosis, which is known to occur throughout the stoke penumbra and in stunned myocardium of AMI. In AMI models, expression of the cardioprotective molecules HSP70 and VEGF are increased. In stroke, equivalent neuroprotective molecules could be up-regulated, preserving tissue and resulting in reduction of infarct volumes. A variety of factors have been implicated in neuroprotection in addition to VEGF, including BDNF, GDNF, EGF, FGF, NT-3, etc. There are a number of factors that could be up-regulated to promote neuronal survival, at least one of which is increased due to NIR light treatment.

Neuroprotection can also result from decreases in toxic factors (e.g., antioxidant protection or by reduction of deleterious factors to tissue function and survival). Regarding antioxidant protection, NIR light may reduce damage induced by free radicals. By-products of free radical damage are found in damaged brain tissue following stroke. This damage is thought to be mediated by neutrophils during reperfusion injury. The nominal spin-trap agent NXY-059 (a free radical scavenger) reduces infarct size if given within 2.25 hours of a stroke (in rat, although it is more effective if given sooner). NIR light can induce the expression of catalase in AMI models. Catalase is a powerful anti-oxidant which can prevent free radical damage and, if produced in the area of the stroke, it may prevent loss via the same mechanism as NXY-059. Axon survival is known to be improved by catalase.

In addition, a number of cytokines and other factors are produced during reperfusion that are deleterious to tissue function and survival. These factors promote activity of existing phagocytic and lymphocytic cells as well as attract additional cells to the area of damage. NIR light can decrease the levels of cytokines in models of neuronal damage. In particular, IL-6 and MCP-1 (pro-inflammatory cytokines) are induced in models of spinal cord damage. NIR light significantly reduces IL-6 and MCP-1 and promotes regrowth of the spinal cords neurons. IL-6 is thought to play a significant role in spinal cord damage in man also.

Regarding neurogenesis, in the last several years, it has been become well-established that the brain has the ability to generate new nerve cells in certain instances. Neural stem cells have been shown to exist in the periventricular areas and in the hippocampus. Naturally-occurring growth factors in the adult human brain can spur the production of new nerve cells from these stem cells. After a stroke, neurogenesis commences in the hippocampus with some cells actually migrating to the damaged area and becoming adult neurons.

NIR light may be effective by either increasing the number of new cells that are formed, or by preventing the loss of the newly formed cells. The latter may be more significant and the majority of newly-formed cells die within 2 to 5 weeks after the stroke (rat model). In an unpublished study by Oron, NIR light has been shown to increase the survival of cardiomyocytes implanted into infarcted heart. Other studies have shown the human neural progenitor cells can be induced to differentiate with stimulation of 810-nanometer irradiation without the presence of specific growth factors that are normally required for differentiation. These data suggest that neurogenesis could occur if the infrared irradiation were to act as a stimulating signal much like a growth factor. Early data from a porcine study of AMI has shown that the 810-nanometer-irradiated pig myocardium showed evidence of cardiogenesis. This result was demonstrated by the presence of significant desmin staining in the laser treated group over control, and by ultrastructural analysis which demonstrated the presence of what appears to be developing cardiomyocytes.

Wavelength Selection

The following section discusses theories and potential action mechanisms, as they presently appear to the inventors, regarding the selection of wavelengths for certain embodiments of phototherapy described herein. The scope of the claims of the present application is not to be construed to depend on the accuracy, relevance, or specifics of any of these theories or potential action mechanisms. Thus the claims of the present application are to be construed without being bound by theory or by a specific mechanism.

In certain embodiments, non-invasive delivery and heating by the electromagnetic radiation place practical limits on the ranges of electromagnetic radiation wavelengths to be used in the treatment of the patient's brain. In certain embodiments, the wavelength of electromagnetic radiation used in the treatment of the patient's brain is selected in view of one or more of the following considerations: (1) the ability to stimulate mitochondrial function in vitro; (2) the ability to penetrate tissue; (3) the absorption in the target tissue; (4) the efficacy in ischemia models in vivo; and (5) the availability of laser sources with the desired power at the desired wavelength or wavelengths. The combination of these effects offers few wavelengths to be used as a therapeutic agent in vivo. These factors can be combined in certain embodiments to create an efficiency factor for each wavelength. Wavelengths around 800 nanometers are particularly efficient. In addition, 808-nanometer light has previously been found to stimulate mitochondrial function and to work in the myocardial infarction models in rat and dog. The following discussion deals with these considerations in more detail.

Photostimulation Effects on Mitochondria

The mitochondria convert oxygen and a carbon source to water and carbon dioxide, producing energy (as ATP) and reducing equivalents (redox state) in the process. The process details of the electron transport chain in mitochondria are schematically diagrammed in <figref idrefs="DRAWINGS">FIG. 37</figref>. The chemical energy released from glucose and oxygen is converted to a proton gradient across the inner membrane of the mitochondria. This gradient is, in turn, used by the ATPase complex to make ATP. In addition, the flow of electrons down the electron transfer chain produces NADPH and NADH (and other factors such as FAD). These cofactors are important for maintaining the redox potential inside the cell within the optimal range. This process has been called the chemi-osmotic theory of mitochondrial function (Dr. Peter Mitchell was awarded a Nobel Prize in chemistry for elucidating these key processes).

There are five large components of the electron transfer chain, Complexes I-IV and the ATPase (also called Complex V), with each complex containing a number of individual proteins (see <figref idrefs="DRAWINGS">FIG. 37</figref>). One of the critical complexes, Complex IV (cytochrome oxidase), is the component responsible for the metabolism of oxygen. The cytochrome C oxidase protein is a key player in the electron transfer in Complex IV through its copper centers. These copper centers have been proposed as important chromophores (photoacceptors) for the absorption of light energy in the near infra-red region.

As an aside, cytochrome C oxidase has enjoyed a renaissance in the last few years as an important factor in the regulation of apoptosis (programmed cell death). Release of cytochrome C oxidase from the mitochondria into the cytosol is a pro-apoptotic signal.

It has been postulated by others that light can directly activate Complex IV and indirectly driving the production of ATP via ATPase (and reducing equivalents). For example, Karu studied the activation spectra of these processes and found that wavelengths that maximally stimulated energy-dependant cellular functions corresponded to the absorption bands of the copper centers in cytochrome C oxidase. <figref idrefs="DRAWINGS">FIG. 38</figref> is a graph of cell proliferation and cytochrome oxidase activity percentage as functions of the wavelength of light used to stimulate mammalian cells. Based on these results, wavelengths of 620, 680, 760, and 820 nanometers (±10 nanometers) promote cellular activities. The 620 and 820 nanometer wavelengths are close to the strongest copper absorption maxima of 635 and 810 nanometers.

Additional data from other groups suggest that cytochrome C oxidase is an important target. Light (670 nanometers) can rescue primary neurons from the toxic effects of the sodium channel blocker tetrodotoxin (TTX). TTX reduces cytochrome oxidase activity in treated neurons, and this reduction is reversed by light treatment (an increase in cytochrome oxidase activity). In an in vivo model, 670 nanometer light is used to rescue retinal function in a methanol-mediated model of retinal damage. Methanol is metabolized to formate, a selective mitochondrial toxin targeted at cytochrome C oxidase. Irradiation with light (670 nanometers) rescued the retina from damage induced by methanol.

Tissue Penetration and Absorption

In vitro and near in vitro like conditions (retinal studies) have previously demonstrated that light can induce beneficial effects in animals. Yet these effects required little if any ability to penetrate non-involved tissues. For treatments of Parkinson's disease by irradiation through intervening tissue, certain embodiments utilize wavelengths that can penetrate to the target tissue.

Light can be absorbed by a variety of chromophores. Some chromophores, such as cytochrome C oxidase can convert the light energy into chemical energy for the cell. Other chromophores can be simple and the light energy is converted to heat, for example water. The absorption of light energy is wavelength dependent and chromophore dependant.

Some chromophores, such as water or hemoglobin, are ubiquitous and absorb light to such a degree that little or no penetration of light energy into a tissue occurs. For example, water absorbs light above approximately 1300 nanometers. Thus energy in this range has little ability to penetrate tissue due to the water content. However, water is transparent or nearly transparent in wavelengths between 300 and 1300 nanometers. Another example is hemoglobin, which absorbs heavily in the region between 300 and 670 nanometers, but is reasonably transparent above 670 nanometers.

Based on these broad assumptions, one can define an “IR window” into the body. Within the window, there are certain wavelengths that are more or less likely to penetrate. This discussion does not include wavelength dependent scattering effects of intervening tissues.

The absorption/transmittance of various tissues have been directly measured to determine the utility of various wavelengths. <figref idrefs="DRAWINGS">FIG. 39</figref> is a graph of the transmittance of light through blood (in arbitrary units) as a function of wavelength. Blood absorbs less in the region above 700 nanometers, and is particularly transparent at wavelengths above 780 nanometers. Wavelengths below 700 nanometers are heavily absorbed, and are not likely to be useful therapeutically (except for topical indications).

<figref idrefs="DRAWINGS">FIG. 40</figref> is a graph of the absorption of light by brain tissue. Absorption in the brain is strong for wavelengths between 620 and 900 nanometers. This range is also where the copper centers in mitochondria absorb. The brain is particularly rich in mitochondria as it is a very active tissue metabolically (the brain accounts for 20% of blood flow and oxygen consumption). As such, the absorption of light in the 620 to 900 nanometer range is expected if a photostimulative effect is to take place.

By combining <figref idrefs="DRAWINGS">FIGS. 39 and 40</figref>, the efficiency of energy delivery as a function of wavelength can be calculated, as shown in <figref idrefs="DRAWINGS">FIG. 41</figref>. Wavelengths between 780 and 880 nanometers are preferable (efficiency of 0.6 or greater) for targeting the brain. The peak efficiency is about 800 to 830 nanometers (efficiency of 1.0 or greater). These wavelengths are not absorbed by water or hemoglobin, and are likely to penetrate to the brain. Once these wavelengths reach the brain, they will be absorbed by the brain and converted to useful energy.

These effects have been directly demonstrated in rat tissues. The absorption of 808 nanometer light was measured through various rat tissues, as shown in <figref idrefs="DRAWINGS">FIG. 42</figref>. Soft tissues such as skin and fat absorb little light. Muscle, richer in mitochondria, absorbs more light. Even bone is fairly transparent. However, as noted above, brain tissue, as well as spinal cord tissue, absorb 808 nanometer light well.

Efficacy in Other Tissues

Two wavelengths have demonstrated efficacy in animal models of ischemia/mitochondrial damage, namely, 670 nanometers and 808 nanometers. Light having a wavelength of 670 nanometers has shown efficacy in retinal damage. Light having a wavelength of 808 nanometers has demonstrated efficacy in animal models of myocardial infarction (as well as soft tissue injury).

The effects of near infrared light on soft tissue injury have been established in FDA approved trials for carpal tunnel syndrome (830 nanometers) and knee tendonitis (830 nanometers). In both cases, 830 nanometer light was superior to placebo for resolution of symptoms.

Light having a wavelength of 808 nanometers was also used to reduce infarct volume and mortality in myocardial infarction (MI) models in rat, dog, and pig. The MI models are particularly relevant to wavelength selection as similar processes—apoptosis, calcium flux, mitochondrial damage—have been implicated in stroke and MI.

Certain wavelengths of light are associated with activation of biological processes, and others are not. In particular, light mediated mitochondrial activation has been used as a marker of biostimulation. Given the lack of in vivo markers, the use of in vitro markers of light activation was used to help narrow down the large number of potential wavelengths. Wavelengths that activate mitochondria were determined, and these wavelengths were used in vivo models.

Penetration to the target tissue is also of importance. If a biological effect is to be stimulated, then the stimulus must reach the target tissue and cell. In this regard, wavelengths between 800 and 900 nanometers are useful, as they can penetrate into the body. In particular, wavelengths of 800 to 830 nanometers are efficient at penetrating to the brain and then being absorbed by the brain.

The use of 808 nanometer light has a solid basis for the treatment of stroke. This wavelength of light can penetrate to the target tissue (brain), is absorbed by the target tissue, stimulates mitochondrial function, and works in a related animal model of ischemia (MI). This supposition is supported by the striking finding that 808 nanometer light can reduce the neurological deficits and infarct volume associated with stroke (in rats).

Other wavelengths have some of these properties. For example, 670 nanometer light can promote mitochondrial function and preserve retinal neurons. However, this wavelength does not penetrate tissue well as it is highly absorbed by hemoglobin. It is therefore not useful in treating stroke or neurodegenerative conditions.

In certain embodiments, wavelengths from 630 to 904 nanometers may be used. This range includes the wavelengths that activate mitochondria in vitro, and that have effects in animal models. These wavelengths also include the predominant bands that can penetrate into the body.

Transmission in Human Brain

Power density measurements have been made to determine the transmission of laser light having a wavelength of approximately 808 nanometers through successive layers of human brain tissue. Laser light having a wavelength of (808±5) nanometers with a maximum output of approximately 35 Watts was applied to the surface of the cortex using a beam delivery system which approximated the beam profile after the laser light passes through the human skull. Peak power density measurements were taken through sections of human brain tissue using an Ocean Optics spectrophotometer Model USB 2000, Serial No. G1965 and beam diameter after scattering was approximated using a Sony Model DCR-IP220, Serial No. 132289.

A fresh human brain and spinal cord specimen (obtained within six hours after death) was collected and placed in physiologic Dakins solution. The pia layer, arachnoid layer, and vasculature were intact. The brain was sectioned in the midline sagittaly and the section was placed in a container and measurements taken at thicknesses of 4.0 centimeters (±0.5 centimeter), 2.5 centimeters (±0.3 centimeter), and 1.5 centimeters (±0.2 centimeter). The power density measurements are shown in Table 2:

<tables id="TABLE-US-00002" num="00002"><table frame="none" colsep="0" rowsep="0"><tgroup align="left" colsep="0" rowsep="0" cols="3"><colspec colname="1" colwidth="35pt" align="center" /><colspec colname="2" colwidth="77pt" align="center" /><colspec colname="3" colwidth="105pt" align="center" /><thead><row><entry namest="1" nameend="3" rowsep="1">TABLE 2</entry></row><row><entry namest="1" nameend="3" align="center" rowsep="1" /></row><row><entry>Thickness</entry><entry>Power density at cortex</entry><entry>Average power density at thickness</entry></row><row><entry namest="1" nameend="3" align="center" rowsep="1" /></row></thead><tbody valign="top"><row><entry>4.0 cm</entry><entry>20 mW/cm²</entry><entry>4.9 μW/cm² </entry></row><row><entry>2.5 cm</entry><entry>20 mW/cm²</entry><entry>20 μW/cm²</entry></row><row><entry>1.5 cm</entry><entry>10 mW/cm²</entry><entry>148 μW/cm² </entry></row><row><entry namest="1" nameend="3" align="center" rowsep="1" /></row></tbody></tgroup></table></tables><br /><figref idrefs="DRAWINGS">FIG. 43</figref> is a graph of the power density versus the depth from the dura for an input power density of 10 mW/cm²with the light bars corresponding to predicted values of the power density and dark bars corresponding to an estimated minimum working power density of 7.5 μW/cm², as described below.

Based upon prior animal experimentation, a conservative estimation of the minimum known power density within the tissue of the brain which is able to show efficacy in stroke animal models is 7.5 μW/cm². This estimated minimum working power density is drawn from an experiment in which 10 mW was applied to the rat brain surface, and 7.5 μW/cm²power density was directly measured 1.8 centimeters from the surface. This stroke model consistently produced significant efficacy, including for strokes 1.8 centimeters from the laser probe. Note that this 7.5 μW/cm²is a conservative estimate; the same power density at the brain surface also consistently produces significant efficacy in the 3 centimeter rabbit clot shower model. Note also that the power density measurements in the human brain experiment do not factor in the effect from the CNS-filled sulci, through which the laser energy should be readily transmitted. However, even conservatively assuming 7.5 μW/cm²as the minimum power density hurdle and ignoring expected transmission benefits from the sulci, the experiment described above confirms that approximately 10-15 mW/cm²transmitted upon the cortex (as per an example dosimetry in man) will be effective to at least 3.0 centimeters from the surface of the brain.

In Vivo Thermal Measurements

In vivo thermal measurements were made to determine the heating effect in living tissue of laser light having a wavelength of approximately 808 nanometers. A GaAlAs laser source of 808-nanometer light was placed in direct contact with the skin of the heads of live rabbits and rats. The laser source had an approximately Gaussian beam profile with a beam diameter of 2.5-4.0 millimeters (1/e²). Thermocouple probes (Model Bat-12 from Physitemp Instruments Inc. of Clifton, N.J.) were placed in the subcutaneous tissue and below the dura and measurements were recorded at various power densities. The results of these measurements are shown in Table 3:

<tables id="TABLE-US-00003" num="00003"><table frame="none" colsep="0" rowsep="0"><tgroup align="left" colsep="0" rowsep="0" cols="5"><colspec colname="1" colwidth="28pt" align="left" /><colspec colname="2" colwidth="49pt" align="left" /><colspec colname="3" colwidth="56pt" align="center" /><colspec colname="4" colwidth="35pt" align="center" /><colspec colname="5" colwidth="49pt" align="left" /><thead><row><entry namest="1" nameend="5" rowsep="1">TABLE 3</entry></row><row><entry namest="1" nameend="5" align="center" rowsep="1" /></row><row><entry /><entry /><entry /><entry>Exposure</entry><entry>Temperature</entry></row><row><entry>Animal</entry><entry>Probe location</entry><entry>Dose</entry><entry>time</entry><entry>increase</entry></row><row><entry namest="1" nameend="5" align="center" rowsep="1" /></row></thead><tbody valign="top"><row><entry>Rat</entry><entry>Subcutaneous</entry><entry>15 mW/cm²</entry><entry>4 minutes</entry><entry>approximately</entry></row><row><entry /><entry /><entry /><entry /><entry>3° C.</entry></row><row><entry>Rat</entry><entry>Subdural</entry><entry>15 mW/cm²</entry><entry>4 minutes</entry><entry>approximately</entry></row><row><entry /><entry /><entry /><entry /><entry>1° C.</entry></row><row><entry>Rat</entry><entry>Subcutaneous</entry><entry>75 mW/cm²</entry><entry>4 minutes</entry><entry>approximately</entry></row><row><entry /><entry /><entry /><entry /><entry>7° C.</entry></row><row><entry>Rat</entry><entry>Subdural</entry><entry>75 mW/cm²</entry><entry>4 minutes</entry><entry>approximately</entry></row><row><entry /><entry /><entry /><entry /><entry>7° C.</entry></row><row><entry>Rabbit</entry><entry>Subcutaneous</entry><entry>7.5 mW/cm² </entry><entry>5 minutes</entry><entry>less than</entry></row><row><entry /><entry /><entry /><entry /><entry>0.5° C.</entry></row><row><entry>Rabbit</entry><entry>Subdural</entry><entry>7.5 mW/cm² </entry><entry>5 minutes</entry><entry>less than</entry></row><row><entry /><entry /><entry /><entry /><entry>0.5° C.</entry></row><row><entry>Rabbit</entry><entry>Subcutaneous</entry><entry>37.5 mW/cm²  </entry><entry>5 minutes</entry><entry>approximately</entry></row><row><entry /><entry /><entry /><entry /><entry>5.5° C.</entry></row><row><entry>Rabbit</entry><entry>Subdural</entry><entry>37.5 mW/cm²  </entry><entry>5 minutes</entry><entry>less than</entry></row><row><entry /><entry /><entry /><entry /><entry>0.5° C.</entry></row><row><entry namest="1" nameend="5" align="center" rowsep="1" /></row></tbody></tgroup></table></tables>

There is minimal heating (e.g., less than 0.5° C.) in the subdural region at four times the therapeutic energy density. The “heat sink” effect of living tissue that minimizes possible heating in the cortex is significantly larger in humans than in rats or rabbits, due to the larger heat sink and blood flow volume, which further limits the undesirable effects of heating in the treated region of the brain. Therefore, in certain embodiments described herein, a therapeutic dosage of energy is delivered to the target area of the brain without undesirable heating of the dura.

Implantation of In Vitro Irradiated Cells

In certain embodiments, a method is provided for treating damage or illness in the central nervous system in a mammal or human, comprising delivering an effective amount of light energy to an in vitro culture comprising progenitor cells, and implanting the cells into the central nervous system of a mammal or human, wherein delivering an effective amount of light energy includes delivering light having a wavelength in the visible to near-infrared wavelength range and a power density of at least about 0.01 mW/cm²to the cells in culture.

In certain embodiments, treatment of a patient includes implantation of progenitor cells into the central nervous system (“CNS”) of the patient. Following implantation, the progenitor cells differentiate to form one or more cell types of the central nervous system. The implanted cells may serve any of a variety of purposes, including replacement of cells or tissues that have been irreparably damaged, repair of a portion of the CNS, enhance the production of important CNS neurochemicals such as dopamine, seratonin, endogenous opioid peptides, and the like. Implantation of progenitor cells may be performed alone, or it may be done in combination with the methods of enhancing neurologic functioning, as described herein.

The term “progenitor cell” as used herein has its broadest reasonable meaning, including but not limited to (1) a pluripotent, or lineage-uncommitted, progenitor cell, a “stem cell” or “mesenchymal stem cell”, that is potentially capable of an unlimited number of mitotic divisions to either renew its line or to produce progeny cells that will differentiate into any of a variety of cells, including cells of the central nervous system including neural cells such as astrocytes, oligodendrocytes, and neurons; or (2) a lineage-committed progenitor cell produced from the mitotic division of a stem cell which will eventually differentiate into a neural cell. Unlike the stem cell from which it is derived, the lineage-committed progenitor is generally considered to be incapable of an unlimited number of mitotic divisions and will eventually differentiate into a neural cell or other CNS cell.

The term “differentiation” as used herein has its broadest reasonable meaning, including but not limited to the process whereby an unspecialized, pluripotent stem cell proceeds through one or more intermediate stage cellular divisions, ultimately producing one or more specialized cell types. Differentiation thus includes the process whereby precursor cells, e.g., uncommitted cell types that precede the fully differentiated forms but may or may not be true stem cells, proceed through intermediate stage cell divisions to ultimately produce specialized cell types. Differentiation encompasses the process whereby mesenchymal stem cells (MSC) are induced to differentiate into one or more of the committed cell types comprising the central nervous system, in vivo or in vitro.

The terms “growth chamber” and “cell culture chamber” as used herein are used interchangeably and are to be interpreted very broadly to refer to any container or vessel suitable for culturing cells, including, but not limited to, dishes, culture plates (single or multiple well), bioreactors, incubators, and the like. Certain embodiments described herein utilize a cell culture apparatus such as is described in U.S. patent application Ser. No. 10/700,355, filed Nov. 3, 2003 and incorporated by reference herein in its entirety.

In certain embodiments, progenitor cells are inoculated and grown in a cell culture in vitro, using parameters including power density as discussed above. Because the light energy is applied directly to the cell culture in vitro and does not travel through intervening body tissue, the power density selected to be delivered to the cell is generally equal to the power density of the light energy as it is emitted from the light apparatus. If lenses, filters, dispersion gratings, or any other material lies between the light source and the cells, any absorption or dispersion of the light energy by such material should be taken into account and the applied light energy adjusted, if needed, to account for the material. In certain embodiments, the treated cells are implanted following treatment. In certain other embodiments, at least some treated cells remain in culture to maintain the cell line for later use.

After in vitro treatment of cells using electromagnetic energy, the cells are transplanted or implanted to a recipient site in a patient. In certain embodiments, the treatment prior to transplantation or implantation includes culturing cells sufficient for implantation. The recipient site may be a site of injury, illness, or defect, or it may be a region of relatively healthy tissue. In certain embodiments, the recipient site and/or the region surrounding such site is treated with light energy according to the methods described supra, before and/or after implantation to enhance the rate at which the implanted cells are integrated with surrounding tissue at the recipient site.

In certain embodiments, progenitor cells such as stem cells are treated with electromagnetic energy as noted above and then implanted into the brain of a patient, such a patient who is at risk for Parkinson's disease, exhibits symptoms of Parkinson's disease, and/or has been diagnosed with Parkinson's disease. Following implantation, the recipient site is optionally treated with electromagnetic energy, including directly at the recipient site or through the skull at the recipient site, or some other portion of the brain, such as the cortex. The transplanted cells produce dopamine to treat, or lessen the symptoms and/or delay onset of Parkinson's disease in the patient.

In certain embodiments, progenitor cells are treated with electromagnetic energy and implanted or transplanted at a site of physical trauma to the spinal cord or one or more nerves of a patient. Following implantation, the recipient site is optionally treated with electromagnetic energy. Such optional treatment may include treatment immediately following implantation and/or one or more treatment periods following implantation. The transplanted cells help repair damage to the spinal cord or nerve(s) such that the recovery or prognosis is enhanced in patients having implanted progenitor cells as compared with those who do not receive such implants.

Treatment of Heat Stroke

In certain embodiments, a method prevents heat stroke in a subject. The term “preventing” in this context includes reducing the severity of a later heat stroke in a subject that has undergone treatment, reducing the incidence of heat stroke in individuals who have undergone treatment, as well as reducing the likelihood of onset heat stroke in a subject that has undergone treatment. The method includes delivering light energy having a wavelength in the visible to near-infrared wavelength range through the skull to at least one area of the brain of a subject, wherein the wavelength, power density and amount of the light energy delivered are sufficient to prevent, reduce the severity, or reduce the incidence of heat stroke in the subject.

While certain embodiments of phototherapy are described herein in conjunction with various theories and potential action mechanisms, as they presently appear to the inventors, the scope of the claims of the present application is not to be construed to depend on the accuracy, relevance, or specifics of any of these theories or potential action mechanisms. Thus the claims of the present application are to be construed without being bound by theory or by a specific mechanism.

Various embodiments of the present invention have been described above. Although this invention has been described with reference to these specific embodiments, the descriptions are intended to be illustrative of the invention and are not intended to be limiting. Various modifications and applications may occur to those skilled in the art without departing from the true spirit and scope of the invention as defined in the appended claims.